EP4233988A2 - Pompes à sang - Google Patents

Pompes à sang Download PDF

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Publication number
EP4233988A2
EP4233988A2 EP23174906.0A EP23174906A EP4233988A2 EP 4233988 A2 EP4233988 A2 EP 4233988A2 EP 23174906 A EP23174906 A EP 23174906A EP 4233988 A2 EP4233988 A2 EP 4233988A2
Authority
EP
European Patent Office
Prior art keywords
impeller
blood
vena cava
pump
cage
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
EP23174906.0A
Other languages
German (de)
English (en)
Other versions
EP4233988A3 (fr
Inventor
Daniel Glozman
Gad LUBINSKY
Ehud Schwammenthal
Yosi Tuval
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Magenta Medical Ltd
Original Assignee
Magenta Medical Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Magenta Medical Ltd filed Critical Magenta Medical Ltd
Publication of EP4233988A2 publication Critical patent/EP4233988A2/fr
Publication of EP4233988A3 publication Critical patent/EP4233988A3/fr
Pending legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/833—Occluders for preventing backflow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/13—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel by means of a catheter allowing explantation, e.g. catheter pumps temporarily introduced via the vascular system
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/135—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting
    • A61M60/139—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting inside the aorta, e.g. intra-aortic balloon pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/205—Non-positive displacement blood pumps
    • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/205—Non-positive displacement blood pumps
    • A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
    • A61M60/237—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller the blood flow through the rotating member having mainly axial components, e.g. axial flow pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/403—Details relating to driving for non-positive displacement blood pumps
    • A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
    • A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
    • A61M60/414—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor transmitted by a rotating cable, e.g. for blood pumps mounted on a catheter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/403—Details relating to driving for non-positive displacement blood pumps
    • A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
    • A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
    • A61M60/416—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor transmitted directly by the motor rotor drive shaft
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/50—Details relating to control
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/515—Regulation using real-time patient data
    • A61M60/531—Regulation using real-time patient data using blood pressure data, e.g. from blood pressure sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/50—Details relating to control
    • A61M60/585—User interfaces
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/804—Impellers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/804—Impellers
    • A61M60/806—Vanes or blades
    • A61M60/808—Vanes or blades specially adapted for deformable impellers, e.g. expandable impellers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
    • A61M60/818—Bearings
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/861—Connections or anchorings for connecting or anchoring pumps or pumping devices to parts of the patient's body

Definitions

  • Some applications of the present invention generally relate to medical apparatus. Specifically, some applications of the present invention relate to apparatus and methods associated with placing a pump in one or more of a subject's renal veins, and/or in the subject's vena cava.
  • cardiac dysfunction or congestive heart failure It is common for cardiac dysfunction or congestive heart failure to develop into kidney dysfunction, which, in turn, causes congestive heart failure symptoms to develop or worsen.
  • systolic and/or diastolic cardiac dysfunction causes systemic venous congestion, which gives rise to an increase in renal venous and interstitial pressure.
  • the increase in the pressure causes fluid retention by the body to increase due both to kidney dysfunction and renal neurohormonal activation, both of which typically develop as a result of the increase in renal venous and interstitial pressure.
  • the resulting fluid retention causes congestive heart failure to develop or worsen, by causing a blood volume overload at the heart and/or by increasing systemic resistance.
  • kidney dysfunction and/or renal neurohormonal activation it is common for kidney dysfunction and/or renal neurohormonal activation to develop into cardiac dysfunction and/or congestive heart failure.
  • This pathophysiological cycle in which cardiac dysfunction and/or congestive heart failure leads to kidney dysfunction and/or renal neurohormonal activation, or in which kidney dysfunction and/or renal neurohormonal activation leads to cardiac dysfunction and/or congestive heart failure, each dysfunction leading to deterioration in the other dysfunction, is called the cardio-renal syndrome.
  • Increased renal venous pressure has been experimentally shown to cause azotemia, and a reduction in glomerular filtration rate, renal blood flow, urine output, and sodium excretion. It has also been shown to increase plasma renin and aldosterone, and protein excretion. Venous congestion may also contribute to anemia via three different pathways: A reduction in the kidney's erythropoietin production, hemodilution by fluid retention, and an inflammatory response leading to a reduced gastro-intestinal iron uptake.
  • renal venous pressure may cause intracapsular pressure and, subsequently, interstitial peritubular pressure, to rise.
  • a rise in peritubular pressure may impact tubular function (reduce sodium excretion), as well as diminish glomerular filtration, by raising the pressure in the Bowman capsule.
  • increased renal venous pressure may not only result from increased central venous (right atrial) pressure, but also from intraperitoneal fluid accumulations (ascites) exerting direct pressure on the renal veins.
  • Reduction of intraabdominal pressure in heart failure patients by removal of fluid has been shown to reduce plasma creatinine levels.
  • Increased venous return resulting from activation of the "leg muscle pump” during physical activity such as walking may raise systemic venous pressure, particularly in heart failure patients, and may result in reflux into the renal veins.
  • a blood pump is placed inside a blood vessel of a subject, the blood pump including (a) an impeller configured to pump blood by rotating, and (b) a support cage that is shaped to define (i) a narrow portion that is configured to be disposed around the impeller, and to maintain a separation between a wall of the blood vessel and the impeller, and (ii) a radial extension from the narrow portion of the support cage that extends radially outward with respect to the narrow portion of the support cage, the extension being configured to substantially maintain a longitudinal axis of the impeller in alignment with a local longitudinal axis of the blood vessel by contacting the wall of the blood vessel.
  • the narrow portion and the radial extension of the support cage are two separately-formed components.
  • the narrow portion and the radial extension of the support cage are separate portions of a single integrated component.
  • the radial extension includes radially-protruding support arms, a bulbous extension that constitutes a radial extension from the narrow portion of the cage, and/or a frustoconical support cage that constitutes a radial extension from the narrow portion of the cage.
  • an impeller that is undersized with respect to the vessel in which it is placed.
  • Such an impeller may be used, for example, in cases in which a larger impeller would undergo a substantial amount of vibration while rotating.
  • such an impeller may be used in cases in which, if the portion of the cage that is configured to separate between the impeller and the vessel wall was larger, there would be a risk that the portion of the cage would become radially compressed by the walls of the vessel, which may result in the impeller becoming deformed (e.g., by the upstream and downstream ends of the impeller axis becoming misaligned), and/or in the impeller becoming misaligned with the local longitudinal axis of the vessel.
  • a narrow portion of the cage surrounds the impeller and is configured to maintain a separation between a wall of the blood vessel and the impeller, for example, in case the vessel narrows, such that, in the absence of the narrow portion of the cage, the walls of the vessel would collapse onto the impeller.
  • the radial extension is typically configured to anchor the blood pump within the vessel by exerting an outward radial force upon the vessel wall, and to substantially maintain a longitudinal axis of the impeller in alignment with a local longitudinal axis of the blood vessel by contacting the wall of the blood vessel.
  • a stiffness of the narrow portion of the cage is greater than that of the radial extension, such that the narrow portion of the cage is configured to maintain the separation between the wall of the blood vessel and the impeller, even if the wall of the vessel exerts pressure upon the support cage that causes the radial extension to deform.
  • material e.g., blood-impermeable material
  • the material is coupled to the support cage such as to contact the vessel wall and to occlude the blood vessel in the region of the blood vessel that surrounds the impeller.
  • the material typically defines a hole therethrough in a central region of the vessel, in a vicinity of the impeller.
  • the material is configured to occlude backflow of blood around the outside of the impeller, but such as to allow antegrade blood flow in the central region of the vessel in the vicinity of the impeller.
  • such a blood pump is configured to be placed within a subject's renal vein and to pump blood from the subject's renal vein into the subject's vena cava, e.g., as described herein with reference to Figs. 13A-B .
  • such a blood pump is configured to be placed within a subject's vena cava upstream of the junctions of the vena cava with all of the subject's renal veins, and to pump blood in a retrograde (i.e., upstream) direction, e.g., as described herein with reference to Fig. 22B .
  • such a blood pump is configured to be placed within a subject's vena cava downstream of the junctions of the vena cava with all of the subject's renal veins, and to pump blood in an antegrade (i.e., downstream) direction, e.g. as described herein with reference to Fig. 22C .
  • an occlusion element is configured to be placed within the subject's vena cava upstream of the junctions of the vena cava with all of the subject's renal veins, and to partially occlude the vena cava, e.g., as described herein with reference to Fig. 22C .
  • upstream and downstream blood pumps are disposed on a single catheter, e.g., as described herein with reference to Figs. 1A-C .
  • an upstream occlusion element, and a downstream blood pump are disposed on a single catheter, e.g., as described herein with reference to Figs. 5A-B , 16 , and 22C .
  • the catheter is introduced into the vena cava from a vein that is above the inferior vena cava (e.g., the jugular vein or the subclavian vein), in which case the upstream pump or occlusion element is disposed upon the catheter distally with respect to the downstream blood pump, as described herein with reference to Figs. 1A and 3 .
  • a vein that is above the inferior vena cava e.g., the jugular vein or the subclavian vein
  • the upstream pump or occlusion element is disposed upon the catheter distally with respect to the downstream blood pump, as described herein with reference to Figs. 1A and 3 .
  • the catheter is introduced into the vena cava from a vein that is below the junctions of the vena cava with the subject's renal veins (e.g., the femoral vein), in which case the upstream pump or occlusion element is disposed upon the catheter proximally with respect to the downstream blood pump, e.g., as described herein with reference to Fig. 4 .
  • an occlusion element and/or a blood pump is placed in a subject's infra-renal vena cava (i.e., within the vena cava, upstream of junctions of the vena cava with all of a subject's renal veins).
  • the occlusion element and/or blood pump is inserted into the vena cava of a subject suffering from acute heart failure.
  • elevated systemic venous pressures cause increased renal parenchymal pressure and increased intraabdominal pressure, factors that can contribute to deterioration of renal perfusion and function.
  • the occlusion element is configured to cause partial occlusion of the infra-renal vena cava, and/or the blood pump is used to pump blood in a retrograde direction within the infra-renal vena cava.
  • use of the occlusion element and/or the blood pump in this manner reduces cardiac preload, by causing lower body venous pooling.
  • reducing cardiac preload ameliorates pulmonary congestion and/or improve cardiac loading conditions and function.
  • an indication of cardiac preload is measured, for example, by measuring central venous pressure, renal venous pressure, cardiac diameter and/or cardiac volume. Further typically, an indication of cardiac output and/or arterial pressure is measured, for example, by measuring arterial blood flow, minute flow, arterial flow velocity, and/or arterial blood pressure.
  • a control unit monitors the indication of cardiac preload, and modulates the extent to which the occlusion element occludes the infra-renal vena cava, and/or the rate at which the blood pump pumps blood, in response thereto.
  • control unit sets the extent to which the occlusion element occludes the infra-renal vena cava, and/or the rate at which the blood pump pumps blood, by determining the highest degree of obstruction, or reverse blood flow, attainable without decreasing cardiac output and/or arterial pressure by more than a given threshold.
  • a downstream pump is placed downstream of the junctions of the vena cava with all of the subject's renal veins, and pumps blood through the vena cava, in the downstream direction, away from the junctions of the vena cava with the renal veins.
  • an occlusion element is placed upstream of the junctions of the vena cava with all of the subject's renal veins and is configured to partially occlude the subject's vena cava upstream of the junctions of the vena cava with the subject's renal veins.
  • the occlusion element is configured to partially occlude the subject's vena cava such that, in response to the pumping of the downstream blood pump, there is not a substantial increase of blood flow from the subject's lower body toward the subject heart, but such that a region of low pressure within the vena cava is generated, between the occlusion element and the downstream blood pump, within which the blood pressure is lower than the subject's central venous pressure.
  • a region of low pressure blood flow from the renal veins into the vena cava increases, thereby lowering renal blood pressure and enhancing renal perfusion.
  • the combination of the downstream pump and the upstream occlusion element is configured such that the overall effect of the downstream pump and the upstream occlusion element is that (a) central venous pressure is lowered relative to lower body venous pressure (e.g., by the pumping of the downstream pump not fully compensating for the reduction in pressure caused by the occlusion of the vena cava by the upstream occlusion element), and (b) renal venous pressure is lowered relative to lower body venous pressure and central venous pressure, due to the region of low pressure being generated within the vena cava, between the occlusion element and the downstream blood pump.
  • the overall effect of the downstream pump and the upstream occlusion element is that (a) central venous pressure is lowered relative to lower body venous pressure (e.g., by the pumping of the downstream pump not fully compensating for the reduction in pressure caused by the occlusion of the vena cava by the upstream occlusion element), and (b) renal venous
  • a control unit controls the extent to which the occlusion element occludes the vena cava and the rate at which the pump pumps blood, responsively to one or more of the parameters detected by sensors. For example, based upon the parameters detected by the sensors, the control unit may control the extent to which the occlusion element occludes the vena cava and the rate at which the pump pumps blood, such that the ratio between renal venous pressure and lower body pressure is a first ratio, and such that the ratio between central venous pressure and lower body pressure is a second ratio, which is different from the first ratio.
  • the first ratio is designated based upon the extent to which it is desirable to decrease the subject's renal venous pressure, such as to increase renal perfusion, in accordance with the techniques described herein.
  • the second ratio is designated based upon the extent to which it is desirable to decrease the subject's cardiac preload, in accordance with the techniques described herein.
  • proximal and related terms when used with reference to a device or a portion thereof, should be interpreted to mean an end of the device or the portion thereof that, when inserted into a subject's body, is typically closer to a location through which the device is inserted into the subject's body.
  • distal when used with reference to a device or a portion thereof, should be interpreted to mean an end of the device or the portion thereof that, when inserted into a subject's body, is typically further from the location through which the device is inserted into the subject's body.
  • downstream and related terms when used with reference to a blood vessel, or with reference to a portion of a device that is configured to be placed inside a blood vessel, should be interpreted to mean a location within the blood vessel, or a portion of the device that is intended for placement at a location within the blood vessel, that is downstream, with respect to the direction of antegrade blood flow through the blood vessel, relative to a different location within the blood vessel.
  • upstream when used with reference to a blood vessel, or with reference to a portion of a device that is configured to be placed inside a blood vessel, should be interpreted to mean a location within the blood vessel, or a portion of the device that is intended for placement at a location within the blood vessel, that is upstream with respect to the direction of antegrade blood flow through the blood vessel, relative to a different location within the blood vessel.
  • apparatus including: a blood pump configured to be placed inside a blood vessel of a subject, the blood pump including:
  • the narrow portion of the support cage and the radial extension include a single integrated component.
  • the narrow portion of the support cage and the radial extension include respective components that are formed separately from each other.
  • the radial extension includes a plurality of radially-protruding support arms that protrude from the narrow portion of the support cage.
  • the radial extension includes a frustoconical cage that is disposed around the narrow portion of the support cage.
  • a stiffness of the narrow portion of the support cage is greater than a stiffness of the radial extension, such that the narrow portion of the cage is configured to maintain the separation between the wall of the blood vessel and the impeller, even if the wall of the vessel exerts pressure upon the support cage that causes the radial extension to deform.
  • the apparatus further includes a material coupled to the support cage, the material defining a hole therethrough in a vicinity of the impeller, the material being configured to occlude backflow of blood around an outside of the impeller, and to allow antegrade blood flow in the vicinity of the impeller.
  • the blood pump is configured to be placed within a renal vein of the subject and to pump blood from the subject's renal vein into a vena cava of the subject.
  • the blood pump is configured to be placed within a vena cava of the subject upstream of junctions of the vena cava with all renal veins of the subject, the pump being configured to pump blood through the vena cava in a retrograde direction.
  • the blood pump is configured to be placed within a vena cava of the subject downstream of junctions of the vena cava with all renal veins of the subject, the pump being configured to pump blood through the vena cava in an antegrade direction.
  • the apparatus further includes an additional blood pump, the additional blood pump being configured to be placed within the subject's vena cava upstream of junctions of the vena cava with all renal veins of the subject, the additional blood pump being configured to pump blood through the vena cava in a retrograde direction.
  • the apparatus further includes an occlusion element configured to be placed within the subject's vena cava upstream of junctions of the vena cava with all renal veins of the subject, the occlusion element being configured to partially occlude blood flow through the vena cava upstream of junctions of the vena cava with all renal veins of the subject.
  • the radial extension includes a bulbous extension that extends radially and distally from the narrow portion of the support cage.
  • a maximum diameter of the bulbous extension when the bulbous extension is in a radially non-constrained configuration thereof, is at least 1.1 times greater than a maximum diameter of the narrow portion of the support cage, when the narrow portion is in a radially non-constrained configuration thereof.
  • apparatus including:
  • the occlusion element includes a balloon configured to be inflated at the infra-renal location
  • the computer processor is configured to modulate the extent to which the occlusion element occludes the vena cava at the infra-renal location by modulating an extent to which the balloon is inflated.
  • the occlusion element includes an expandable frame having material covered thereto, and the computer processor is configured to modulate the extent to which the occlusion element occludes the vena cava at the infra-renal location by modulating an extent to which the frame is expanded.
  • the occlusion element includes a nozzle
  • the computer processor is configured to modulate the extent to which the occlusion element occludes the vena cava at the infra-renal location by modulating a diameter of an opening of the nozzle.
  • the one or more sensors are configured to monitor a parameter of the subject that is indicative of cardiac output of the subject, and the computer processor is configured to modulate the extent to which the occlusion element occludes the vena cava at the infra-renal location responsively to the parameter that is indicative of the cardiac output.
  • the one or more sensors include a thermodilution catheter configured to monitor the parameter that is indicative of the cardiac output.
  • the one or more sensors are further configured to monitor a parameter of the subject that is indicative of cardiac preload of the subject, and the computer processor is configured to modulate the extent to which the occlusion element occludes the vena cava at the infra-renal location responsively to the parameter that is indicative of the cardiac output in combination with the parameter that is indicative of the cardiac preload.
  • the one or more sensors are configured to monitor a parameter of the subject that is indicative of arterial blood pressure of the subject, and the computer processor is configured to modulate the extent to which the occlusion element occludes the vena cava at the infra-renal location responsively to the parameter that is indicative of the arterial blood pressure.
  • the one or more sensors are further configured to monitor a parameter of the subject that is indicative of cardiac preload of the subject, and the computer processor is configured to modulate the extent to which the occlusion element occludes the vena cava at the infra-renal location responsively to the parameter that is indicative of the arterial blood pressure in combination with the parameter that is indicative of the cardiac preload.
  • the apparatus further includes a blood pump configured to be placed at a location within the vena cava that is downstream of junctions of the vena cava with all renal veins of the subject, the blood pump being configured to reduce the subject's renal venous pressure relative to the subject's central venous pressure by pumping blood in an antegrade direction through the vena cava from the location.
  • a blood pump configured to be placed at a location within the vena cava that is downstream of junctions of the vena cava with all renal veins of the subject, the blood pump being configured to reduce the subject's renal venous pressure relative to the subject's central venous pressure by pumping blood in an antegrade direction through the vena cava from the location.
  • the computer processor is further configured to modulate a rate at which the blood pump pumps blood in the antegrade direction, responsively to the one or more physiological parameters.
  • the computer processor is configured to modulate the rate at which the blood pump pumps blood in the antegrade direction responsively to the one or more physiological parameters in coordination with modulating the extent to which the vena cava is occluded at the infra-renal location responsively to the one or more physiological parameters, such as to:
  • apparatus including:
  • the one or more sensors are configured to monitor a parameter of the subject that is indicative of cardiac output of the subject, and the computer processor is configured to modulate the rate at which the blood pump pumps blood in the retrograde direction responsively to the parameter that is indicative of the cardiac output.
  • the one or more sensors include a thermodilution catheter configured to monitor the parameter that is indicative of the cardiac output.
  • the one or more sensors are further configured to monitor a parameter of the subject that is indicative of cardiac preload of the subject, and the computer processor is configured to modulate at which the blood is pumped includes modulating the rate at which the blood pump pumps blood in the retrograde direction responsively to the parameter that is indicative of the cardiac output in combination with the parameter that is indicative of the cardiac preload.
  • the one or more sensors are configured to monitor a parameter of the subject that is indicative of arterial blood pressure of the subject, and the computer processor is configured to modulate the rate at which the blood pump pumps blood in the retrograde direction responsively to the parameter that is indicative of the arterial blood pressure.
  • the one or more sensors are further configured to monitor a parameter of the subject that is indicative of cardiac preload of the subject, and the computer processor is configured to modulate at which the blood is pumped includes modulating the rate at which the blood pump pumps blood in the retrograde direction responsively to the parameter that is indicative of the arterial blood pressure in combination with the parameter that is indicative of the cardiac preload.
  • the apparatus further includes a second blood pump configured to be placed at a downstream location within the vena cava that is downstream of junctions of the vena cava with all renal veins of the subject, the second blood pump being configured to reduce the subject's renal venous pressure relative to the subject's central venous pressure by pumping blood in an antegrade direction through the vena cava from the location that is downstream of junctions of the vena cava with all renal veins of the subject.
  • a second blood pump configured to be placed at a downstream location within the vena cava that is downstream of junctions of the vena cava with all renal veins of the subject, the second blood pump being configured to reduce the subject's renal venous pressure relative to the subject's central venous pressure by pumping blood in an antegrade direction through the vena cava from the location that is downstream of junctions of the vena cava with all renal veins of the subject.
  • the computer processor is further configured to modulate a rate at which the second blood pump pumps blood in the antegrade direction from the downstream location, responsively to the one or more physiological parameters.
  • the computer processor is configured to modulate the rate at which the second blood pump pumps blood in the antegrade direction from the downstream location responsively to the one or more physiological parameters by modulating the rate at which the blood is pumped in the antegrade direction through the vena cava from the downstream location in coordination with modulating the rate at which blood is pumped in the retrograde direction at the infra-renal location within the subject's vena cava, such as to:
  • Figs. 1A-C are schematic illustrations of a blood-pump catheter 20 placed within a subject's vena cava 22, via a guide catheter 23, an upstream pump 24U being disposed upon the catheter, distally to a downstream pump 24D, in accordance with some applications of the present invention.
  • the distal portion of blood-pump catheter 20 is configured to be straight, when the catheter is in a non-constrained state, such that both the upstream and the downstream pumps are disposed along the axis of the catheter, within the vena cava.
  • Each of the upstream and downstream pumps 24U and 24D typically includes a radially-expandable impeller 28 disposed inside a radially-expandable impeller cage 30.
  • impeller 28 and impeller cage 30 are shape-set such as to assume radially expanded configurations thereof in the absence of any radially constraining force acting upon the impeller and the cage.
  • the blood pumps are inserted into the subject's vena cava, while the blood pumps are in radially constrained configurations inside the guide catheter, and are configured to assume substantially radially non-constrained configurations by being released from the guide catheter inside the subject's vena cava.
  • an engagement mechanism engages the impeller and the cage with respect to one another, such that in response to the cage becoming radially constrained, the impeller becomes radially constrained, e.g., in accordance with apparatus and methods described in described in US 2016/0022890 to Schwammenthal , which is incorporated herein by reference.
  • the term "impeller” is generally used herein to denote a bladed rotor, as shown in Figs. 1A-C , for example.
  • a blood vessel such as vena cava 22
  • the bladed rotor functions as an impeller, by modifying the flow of blood through the blood vessel, and/or by generating a pressure difference between the upstream end and the downstream end of the impeller.
  • reference numeral 24 is generally used to denote a blood pump in the present application.
  • reference numeral 24U When a pump that is placed upstream is being referred to, reference numeral 24U is used, and when a pump that is placed downstream is being referred to, reference numeral 24D is used.
  • reference numeral 28 is generally used to denote an impeller in the present application. When an impeller that is placed upstream is being referred to, reference numeral 28U is used, and when an impeller that is placed downstream is being referred to, reference numeral 28D is used.
  • Blood-pump catheter 20 is typically placed inside the subject's vena cava 22, and operated therein, in order to provide acute treatment of a subject suffering from cardiac dysfunction, congestive heart failure, low renal blood flow, high renal vascular resistance, arterial hypertension, diabetes, and/or kidney dysfunction.
  • the blood-pump catheter may be placed inside the subject's vena cava, and operated therein, for a period of more than one hour (e.g., more than one day), less than one week (e.g., less than four days), and/or between one hour and one week (e.g., between one day and four days).
  • the blood-pump catheter is chronically placed inside the subject's vena cava in order to provide chronic treatment of a subject suffering from cardiac dysfunction, congestive heart failure, low renal blood flow, high renal vascular resistance, arterial hypertension, diabetes, and/or kidney dysfunction.
  • a course of treatment is applied to a subject over several weeks, several months, or several years, during which the blood-pump catheter is intermittently placed inside the subject's vena cava, and the subject is intermittently treated in accordance with the techniques described herein.
  • the subject may be intermittently treated at intervals of several days, several weeks, or several months.
  • blood-pump catheter 20 is inserted into vena cava 22, via the subject's subclavian vein 40, as shown in Fig. 1A .
  • the blood-pump catheter is inserted under fluoroscopic imaging.
  • the blood-pump catheter is inserted under ultrasound imaging, such as to reduce exposure of the subject to radiation and/or contrast agent.
  • the catheter is placed into the vena cava such that upstream pump 24U is disposed upstream of the junctions of the vena cava and all of the subject's renal veins 42, and such that downstream pump 24D is disposed downstream of the junctions of the vena cava and all of the subject's renal veins.
  • the upstream pump is configured to pump blood through the vena cava in the upstream direction, away from the renal veins
  • the downstream pump is configured to pump blood through the vena cava in the downstream direction, away from the renal veins.
  • the effect of both of pumps 24U and 24D pumping blood in the above-described manner is that, between the pumps, and adjacent to the junctions of the vena cava with the renal veins, there is a low-pressure region of the vena cava, within which blood pressure is lower than the subject's central venous pressure. Functionally, this region may be viewed as a compartment within the vena cava within which blood pressure is controlled (by controlling pumps 24U and 24D), regardless of the blood pressure elsewhere within the vena cava. This typically increases blood flow from the renal veins into the vena cava, lowers pressure within the subject's renal veins, and causes renal perfusion to increase.
  • the effect of pumps 24U and 24D on blood flow through the renal veins and the vena cava is indicated by arrows 44 in Fig. 1B .
  • the effect of operating blood pumps 24U and 24D is that between the pumps there is a low-pressure region of the vena cava.
  • the pumps are operated simultaneously such that the pressure within other portions of the vena cava is substantially unchanged relative to when blood-pump catheter 20 is not in operation.
  • the pumps are typically operated simultaneously such that the pressure within the vena cava downstream of downstream pump 24D is not substantially increased relative to when blood-pump catheter 20 is not in operation.
  • the pumps are typically operated simultaneously such that the pressure within the vena cava upstream of upstream pump 24U is not substantially increased relative to when blood-pump catheter 20 is not in operation.
  • the pumps are typically operated simultaneously such that venous return to the vena cava from regions upstream of the upstream pump and downstream from the downstream pump is substantially unchanged relative to when blood-pump catheter 20 is not in operation.
  • the pumps are typically operated simultaneously such as to have a generally synergistic effect on pressure and flow in the region between the pumps, but to have an antagonistic effect on pressure and flow outside of the region, such that, outside of the region, the effects of the two pumps typically substantially cancel each other out.
  • blood-pump catheter 20 pumps blood in a manner that enhances the rate of blood flow through the renal veins and into the vena cava, but does not cause a substantial change in the direction of the blood flow relative to the natural direction of flow through the renal veins, or from the renal veins to the vena cava (i.e., relative to blood flow in the absence of pumping by the blood-pump catheter). That is to say, the blood-pump catheter pumps blood in the downstream direction through the renal veins and then directly into the portion of the vena cava that is adjacent to the renal veins, rather than, for example, pumping the blood from the renal veins into a different portion of the subject's veins (such as, an upstream location within the vena cava).
  • blood-pump catheter 20 enhances blood flow through the renal veins without removing blood from the subject's venous system into a non-venous receptacle, such as an artificial lumen of a blood pump.
  • typically blood-pump catheter 20 is placed inside the vena cava of a subject suffering from cardiac dysfunction, congestive heart failure, low renal blood flow, high renal vascular resistance, arterial hypertension, diabetes, and/or kidney dysfunction.
  • operating the blood-pump catheter in the vena cava of such a subject causes a lowering and flattening of the subject's renal vein pressure profile, even though the subject's central venous pressure is elevated and has additional effects, e.g., as described with reference to Fig. 4B of US 2016/0022890 to Schwammenthal , which is incorporated herein by reference.
  • each of upstream and downstream pumps 24U and 24D includes an impeller 28, for example, any one of the impellers described in US 2016/0022890 to Schwammenthal , which is incorporated herein by reference.
  • impeller 28 may have a single blade, two blades (e.g., as described in US 2016/0022890 to Schwammenthal , which is incorporated herein by reference), three blades (e.g., as described in US 2016/0022890 to Schwammenthal ), or more than three blades.
  • one or both of blood pumps 24U and 24D includes more than one impeller.
  • ceteris paribus by using more than one impeller in at least one of the pumps, in order to generate a given flow of blood with the pump, the force that impacts each of the impellers within the pump is smaller than if a single impeller were to be used in the pump.
  • one or both of the pumps includes radially expandable impeller cage 30.
  • impeller cage 30 is configured to hold open the inner wall of the vena cava and to separate the inner wall of the vena cava from the impeller, such that the vena cava does not become injured by the impeller.
  • the impeller cage is sized such that the cage is not used to hold open the inner wall of the vena cava (the diameter of the cage being less than that of the vena cava, at least in some subjects).
  • the cage typically functions to separate the inner wall of the vena cava from the impeller, for example, in case the walls of the vena cava at least partially collapse inwardly, such that the vena cava does not become injured by the impeller.
  • Such applications are described with reference to Figs. 9A-B , for example.
  • impeller 28 and cage 30 are shape-set such as to assume radially expanded configurations thereof in the absence of any radially constraining force acting upon the impeller and/or the cage.
  • an engagement mechanism engages the impeller and the cage with respect to one another, such that in response to the cage becoming radially constrained the impeller becomes radially constrained, e.g., in accordance with apparatus and methods described in described in US 2016/0022890 to Schwammenthal , which is incorporated herein by reference.
  • the stiffness of cage 30 is sufficiently great that pressure exerted upon the cage by the inner wall of the vena cava does not deform the cage. The cage thereby protects the impeller from being deformed by pressure from the inner wall of the vena cava.
  • impeller 28 and impeller cage 30 are substantially radially non-constrained, due to the relatively low radial force exerted by the vena cava wall on the cage.
  • the impeller and/or impeller cage may not be fully radially non-constrained, due to the walls of the vena cava applying a radially compressive force to the blood pumps.
  • the impeller cage is configured to come into contact with the inner wall of the vena cava, when the impeller cage assumes its radially non-constrained configuration inside the vena cava, e.g., as shown in Fig. 1C .
  • a span SP of impeller 28, when the impeller is in a non-constrained configuration thereof inside the vena cava is more than 14 mm (e.g., more than 16 mm), and/or less than 28 mm (e.g., less than 22 mm), e.g., 14-28 mm, or 16-22 mm.
  • a diameter D of cage 30, when the cage is in a non-constrained configuration thereof inside the vena cava is more than 14 mm (e.g., more than 16 mm), and/or less than 40 mm (e.g., less than 35 mm), e.g., 14-40 mm, or 16-35 mm.
  • a longitudinal distance D1 between centers of the impellers of the upstream and downstream pumps, measured along the longitudinal axis of the catheter is typically more than 3 cm (e.g., more than 6 cm), and/or less than 18 cm (e.g., less than 14 cm), e.g., 3-18 cm, or 6-14 cm.
  • distance D1 is adjustable and is set based upon measurements that are performed upon a subject.
  • impeller cage 30 is configured such that in its radially non-constrained configuration, the cage has a diameter that is less than that of the vena cava at least in some subjects, for example, as described hereinbelow with reference to Figs. 9A-B .
  • impellers 28 of upstream and downstream pumps 24U and 24D are rotated at respective rotation rates, in order to cause the pumping of blood in the upstream and downstream directions to be performed at respective rates.
  • the impellers are rotated at the same rotation rate (and, typically, in the same direction), but the impellers are sized, shaped, and/or oriented such that the rate at which blood is pumped, respectively, in the upstream and downstream directions, by the respective impellers, is not equal.
  • a control unit 52 and a user interface 54 are disposed outside the subject's body. Further typically, the control unit receives inputs from one or more pressure sensors 56, 58, and/or 60, e.g., as shown in Figs. 1A-C .
  • blood-pump catheter 20 includes pressure sensor 58 disposed between the two blood pumps, and is configured to measure pressure within the low-pressure region of the vena cava between the two blood pumps, which is typically indicative of blood pressure within the subject's renal veins, and the blood-pump catheter does not include pressure sensor 56, or pressure sensor 60.
  • control unit 52 controls pumps 24U and 24D, e.g., by controlling rotation of impellers 28, responsively to one or more of the above-described inputs.
  • user interface 54 displays the subject's current lower-body venous pressure, renal venous pressure, and/or central venous pressure, based upon the signals generated by sensors 56, 58, and/or 60.
  • a user based upon the current values of the subject's lower-body venous pressure, renal venous pressure, and/or central venous pressure, a user (such as a healthcare professional) inputs a target value for the subject's renal venous pressure, via the user interface.
  • control unit 52 controls the speed of the rotation of the impellers, such that the impellers pump blood away from the renal veins at a flow rate that is such as to reduce the renal venous pressure toward the target level, as indicated by the user.
  • the control unit stops the impellers rotating.
  • the control unit receives an input from an additional sensor (such as a flow sensor and/or an oxygen-saturation sensor, and/or a thermal flow sensor, e.g., as described with reference to Figs. 22Ai-22C ii of US 2016/0022890 to Schwammenthal , which is incorporated herein by reference), and the control unit controls the speed of the rotation of the impellers responsively to an input from the additional sensor.
  • an additional sensor such as a flow sensor and/or an oxygen-saturation sensor, and/or a thermal flow sensor, e.g., as described with reference to Figs. 22Ai-22C ii of US 2016/0022890 to Schwammenthal , which is incorporated herein
  • control unit 52 typically includes a computer processor that comprises circuitry and that is configured to execute the actions described herein.
  • the operations described herein that are performed by the computer processor transform the physical state of a memory, which is a real physical article that is in communication with the computer processor, to have a different magnetic polarity, electrical charge, or the like, depending on the technology of the memory that is used.
  • Control unit 52 is typically a hardware device programmed with computer program instructions to produce a special-purpose computer. For example, when programmed to perform the techniques described herein, control unit 52 typically acts as a special-purpose, renal-venous-pressure-modulating computer processor.
  • user interface 54 typically includes any type of user interface configured to receive inputs from a user and/or to provide outputs to the user.
  • the user interface may include one or more input devices (such as a keyboard, a mouse, a trackball, a joystick, a touchscreen monitor, a touchpad, a voice-command interface, a smartphone, a tablet computer, and/or other types of input devices that are known in the art), and/or one or more output devices (such as a monitor, an audio output device, a smartphone, a tablet computer, and/or other types of output devices that are known in the art).
  • input devices such as a keyboard, a mouse, a trackball, a joystick, a touchscreen monitor, a touchpad, a voice-command interface, a smartphone, a tablet computer, and/or other types of input devices that are known in the art
  • output devices such as a monitor, an audio output device, a smartphone, a tablet computer, and/or other types of output devices that are known in the art.
  • FIGs. 2A, 2B, 2C , 2D, and 2E are schematic illustrations of arrangements of impellers 28U and 28D that are configured to pump blood in opposite directions from one another, in accordance with some applications of the present invention.
  • Figs. 2A-E show the impellers in the absence of impeller cages, although typically, the impellers are used together with impeller cages 30, as described hereinabove.
  • impellers of pumps 24U and 24D are coupled to one or more motors 46 ( Fig. 1A ), which impart rotational motion to the impellers, via one or more rotation shafts, the shaft(s) being housed inside blood-pump catheter 20.
  • the motors are disposed outside of the subject's body (as shown), or are placed inside the subject's body (not shown).
  • impellers 28 of upstream and downstream pumps 24U and 24D are rotated in the same rotational direction as one another, as viewed from an external reference point (e.g., in the direction of arrow 48 (i.e., clockwise), or counterclockwise), but the impellers are disposed on the catheter such that the rotation of the impellers in this direction of rotation causes the impellers to pump blood in respective, opposite directions.
  • an external reference point e.g., in the direction of arrow 48 (i.e., clockwise), or counterclockwise
  • the rotational direction of the impellers "as viewed from an external reference point” should be interpreted to mean the direction of rotational motion of the impellers as observed from any point that is not undergoing the same rotational motion as either of the impellers.
  • a single motor is used to rotate both of the impellers.
  • a shaft 50 is used to impart the rotational motion from the motor to the proximal impeller.
  • An additional shaft 51 which is in series with shaft 50, couples the proximal impeller to the distal impeller and imparts the rotational motion from the proximal impeller to the distal impeller.
  • the diameter of blood-pump catheter 20 is reduced relative to if parallel shafts were used, in order to impart rotation to the upstream and downstream impellers.
  • angles and/or orientations of the impeller blades of impellers 28 of upstream and downstream pumps 24U and 24D may be such as to cause the impellers to pump blood in respective, opposite directions.
  • each impeller is shaped and/or oriented in the mirror image of the other, the axis of reflection being orthogonal to the longitudinal axes of the impellers.
  • the upstream and downstream impellers are of opposing handedness to one another, a first one of the impellers being a left-handed impeller, and the other one of the impellers being a right-handed impeller.
  • impellers of opposing handedness that are positioned parallel to one another, facing the same direction as one another, and rotating in opposite rotational directions from one another, generate flow in the same direction as one another.
  • the upstream and downstream impellers are disposed upon shaft 51 such that the impellers are facing in opposite directions to one another.
  • the impellers are typically rotated in the same rotational direction as one another, as viewed from an external reference point.
  • the result of the impellers (a) being of opposing handedness to one another, and (b) facing in opposite directions, is that, when the impellers are rotated in the same direction as one another about an axis defined by shaft 51, the impellers pump blood in opposite directions from one another.
  • the blades of the downstream impeller are oriented such that, as the downstream impeller rotates in the direction of arrow 48, the downstream impeller pumps in the downstream direction.
  • the blades of the upstream impeller are oriented such that, as the upstream impeller rotates in the direction of arrow 48, the upstream impeller pumps in the upstream direction.
  • the upstream impeller 28U and the downstream impeller 28D are rotated in opposite directions from one another, as viewed from an external reference point, in order to generate blood flow in opposite directions from one another.
  • impellers that are of the same handedness as one another and that are facing the same direction as one another may be used.
  • a single motor is used to rotate both of the impellers.
  • Shaft 50 is used to impart the rotational motion from the motor to the proximal impeller.
  • Additional shaft 51 which is in series with shaft 50, couples the proximal impeller to the distal impeller and imparts the rotational motion from the proximal impeller to the distal impeller.
  • a gear mechanism 70 is disposed between the proximal impeller and the distal impeller (e.g., along shaft 51, as shown), and is configured to reverse the direction of rotational motion that is imparted from the proximal impeller to the distal impeller, such that the distal impeller rotates in an opposite direction of rotation to the direction of rotation of the proximal impeller.
  • the downstream impeller which in this case is the proximal impeller
  • the upstream impeller rotates in the direction of arrow 72 (i.e., the opposite direction to that of arrow 48).
  • downstream impeller it is advantageous to rotate the downstream impeller in the opposite direction from the upstream impeller (e.g., as shown in Fig. 2B ), rather than rotating the downstream impellers in the same direction as the upstream impeller (e.g., as shown in Fig. 2A ).
  • downstream impeller rotates in the same direction as the upstream impeller, then blood flowing through the vena cava that impacts the downstream impeller is already at least partially undergoing rotational motion in the direction of rotation of the downstream impeller (by virtue of the rotational motion imparted to the blood flow by the upstream impeller).
  • the upstream and downstream impellers are configured to pump blood in opposite directions from one another by rotating in opposite directions from one another, e.g., using techniques described with reference to any one of Figs. 2B , 2D, or 2E .
  • impellers 28 of upstream and downstream pumps 24U and 24D are rotated in the same rotational direction as one another, as viewed from an external reference point (e.g., in the direction of arrow 48 (i.e., clockwise), or counterclockwise), but the impellers are disposed on the catheter such that the rotation of the impellers in this direction of rotation causes the impellers to pump blood in respective, opposite directions.
  • the configuration shown in Fig. 2C is generally similar to that of Fig. 2A , with the impellers being of opposing handedness to one another, and facing in opposite directions to one another. However, in the configuration shown in Fig.
  • an additional impeller 74 is disposed between the upstream and the downstream impellers. Impeller 74 is configured not to be actively rotated. As indicated by the two-dimensional arrows indicating the direction of blood flow, blood that is rotated by the upstream impeller impacts impeller 74, causing the rotational motion of the blood flow to be at least partially reduced. Due to the reduction in the rotational motion of the blood flow, the effect of the rotation of the downstream impeller upon the blood flow is greater than it would be in the absence of impeller 74.
  • motor 46 is used to rotate a first one of the impellers in a first direction.
  • motor 46 is used to rotate downstream impeller 28D in the direction of arrow 48 (i.e., clockwise).
  • a second motor 75 is used to rotate the second one of the impellers in the opposite direction to the first direction.
  • motor 75 is used to rotate upstream impeller 28U in the direction of arrow 72 (i.e., counterclockwise).
  • a first rotation shaft 76 extends from first motor 46 to the first impeller and imparts the rotational motion in the first direction to the first impeller.
  • a second rotation shaft 78 extends from second motor 75 to the second impeller and imparts the rotational motion in the opposite direction to the first direction to the second impeller.
  • first rotation shaft 76 and second rotation shaft 78 are coaxial with one another, as shown.
  • impellers that are of the same handedness as one another are used as the upstream impeller 28U and the downstream impeller 28D.
  • Fig. 2E is a schematic illustration of upstream and downstream pumps 24U and 24D being disposed on respective catheters 66 and 68, in accordance with some applications of the present invention.
  • a first catheter 66 is inserted into vena cava 22 through a guide catheter 67 that is inserted via the subject's femoral vein, or via another vein that is below the subject's inferior vena cava.
  • Upstream blood pump 24U is disposed on the first catheter, and is configured to be placed within the vena cava upstream of the junctions of the vena cava with all of the subject's renal veins, and to pump blood through the vena cava in the manner described hereinabove.
  • a second catheter 68 is inserted into the vena cava through a guide catheter 69 that is inserted via the subject's jugular vein, subclavian vein, or via a different vein that is above the subject's inferior vena cava.
  • Downstream blood pump 24D is disposed on the second catheter, and is configured to be placed within the vena cava downstream of the junctions of the vena cava with all of the subject's renal veins, and to pump blood through the vena cava in the manner described hereinabove.
  • motors 46 and 75 are used to control rotation of the impellers.
  • motor 46 rotates the downstream pump in a first direction (e.g., the direction of arrow 48)
  • motor 75 rotates the upstream pump in the opposite direction (e.g., the direction of arrow 72).
  • control unit 52 Fig. 1A
  • controls both pumps e.g., by controlling the rates of rotation of the impellers).
  • pressure sensors 56, 58 and 60 are disposed upon the first and/or second catheters, and are configured to detect indications of, respectively, lower body venous pressure, renal venous pressure, and central venous pressure.
  • the control unit is configured to control the operation of the upstream and downstream pumps responsively to the detected indications, in accordance with the techniques described hereinabove.
  • the impellers of the upstream and downstream pumps are configured to pump blood in the same direction as one another, e.g., in the antegrade direction to enhance blood flow through a vessel.
  • FIG. 3 is a schematic illustration of blood-pump catheter 20 being inserted into the subject's vena cava 22 via the subject's right jugular vein 62 (through guide catheter 23), in accordance with some applications of the present invention.
  • blood-pump catheter 20 is inserted into the vena cava via the subject's right jugular vein, or via another vein that is above the subject's inferior vena cava.
  • blood-pump catheter 20 and the functioning thereof are generally as described with reference to Figs. 1A-C .
  • FIG. 4 is a schematic illustration of blood-pump catheter 20 being inserted into the subject's vena cava 22 via the subject's femoral vein 64 (through guide catheter 23), downstream pump 24D being disposed upon the catheter distally to upstream pump 24U, in accordance with some applications of the present invention.
  • blood-pump catheter 20 is inserted into the vena cava, via the subject's femoral vein 64, or via another vein that is below the subject's inferior vena cava.
  • downstream blood pump 24D is disposed on blood-pump catheter 20 distally to upstream blood pump 24U.
  • Blood-pump catheter 20 is configured to be placed within the vena cava, such that the upstream pump is disposed upstream of the junctions of the vena cava with all of the subject's renal veins 42, and such that the downstream pump is disposed downstream of the junctions of the vena cava with all of the subject's renal veins.
  • blood-pump catheter 20 is generally similar to that described with reference to blood-pump catheter 20 as shown in Figs. 1A-C .
  • Figs. 5A-B are schematic illustrations of blood-pump catheter 20, the catheter including downstream pump 24D and an occlusion element, such as a balloon 80 ( Fig. 5A ), or a covered frame 82 ( Fig. 5B ), in accordance with some applications of the present invention.
  • a nozzle is used as the upstream occlusion element, e.g., as described in co-pending PCT Patent Application No. PCT/IL2017/051092 to Tuval, filed Sep. 28, 2017 , which is incorporated herein by reference.
  • downstream pump is placed inside vena cava 22, downstream of the junctions of the vena cava with all of the subject's renal veins.
  • the downstream pump pumps blood through the vena cava, in the downstream direction, away from the junctions of the vena cava with the renal veins, in the manner described hereinabove.
  • the occlusion element is placed inside the vena cava upstream of the junctions of the vena cava with the subject's renal veins.
  • the occlusion element is configured to partially occlude the subject's vena cava upstream of the junctions of the vena cava with the subject's renal veins.
  • the occlusion element is configured to partially occlude the subject's vena cava such that, in response to the pumping of the downstream blood pump, there is not a substantial increase of blood flow from the subject's lower body toward the subject heart, but such that a region of low pressure within the vena cava is generated, between the occlusion element and the downstream blood pump, within which the blood pressure is lower than the subject's central venous pressure.
  • a region of low pressure blood flow from the renal veins into the vena cava increases, thereby lowering renal blood pressure and enhancing renal perfusion.
  • the occlusion element is configured to partially occlude, but not to totally occlude, the vena cava, in such a manner as to generate a region of low pressure within the vena cava, but to allow a substantial flow of blood through the vena cava.
  • a longitudinal distance D2 between the longitudinal center of the impeller of the downstream pump and the longitudinal center of the occlusion element, measured along the longitudinal axis of the catheter is typically more than 3 cm (e.g., more than 6 cm), and/or less than 18 cm (e.g., less than 14 cm), e.g., 3-18 cm, or 6-14 cm.
  • the occlusion element is balloon 80, as shown in Fig. 5A .
  • the occlusion element is covered frame 82, as shown in Fig. 5B .
  • the frame may be a frame (e.g., a rigid or semi-rigid frame) made of a shape-memory element (such as nitinol) that is covered with a material (e.g., a blood-impermeable material) 83 (e.g., polyester, polyurethane, and/or a different polymer).
  • a material e.g., a blood-impermeable material
  • the occlusion element is configured to partially occlude the vena cava upstream of the junctions of the vena cava with the subject's renal veins.
  • the diameter to which the occlusion element is expanded is controllable.
  • inflation of the balloon may be controllable, or the frame may be expandable (e.g., by heating the frame, or by applying an electrical current to the frame).
  • control unit 52 responsively to the blood pressure detected by blood pressure sensor 56, 58, and/or 60, in response to an input from a different sensor (such as a flow sensor and/or an oxygen-saturation sensor, and/or a thermal flow sensor, e.g., as described with reference to Figs. 22Ai-C ii of US 2016/0022890 to Schwammenthal , which is incorporated herein by reference), and/or in response to an input from a user.
  • a control unit e.g., control unit 52
  • the rate at which pump 24D pumps blood away from the renal veins is controlled by a control unit responsively to the blood pressure detected by blood pressure sensor 56, 58, and/or 60, in response to an input from a different sensor (such as a flow sensor and/or an oxygen-saturation sensor, and/or a thermal flow sensor, e.g., as described with reference to Figs. 22Ai-C ii of US 2016/0022890 to Schwammenthal , which is incorporated herein by reference), and/or in response to an input from a user.
  • a control unit responsively to the blood pressure detected by blood pressure sensor 56, 58, and/or 60, in response to an input from a different sensor (such as a flow sensor and/or an oxygen-saturation sensor, and/or a thermal flow sensor, e.g., as described with reference to Figs. 22Ai-C ii of US 2016/0022890 to Schwammenthal , which is incorporated herein by reference), and/or in response
  • Figs. 5A and 5B show the downstream blood pump and the occlusion element disposed on a catheter that is inserted into the vena cava from above the junctions of the vena cava with the subject's renal veins (e.g., via the subject's subclavian vein or jugular vein), for some applications, the downstream blood pump and the occlusion element are disposed on a catheter that is inserted into the vena cava from below the junctions of the vena cava with the subject's renal veins (e.g., via the subject's femoral vein), mutatis mutandis.
  • the occlusion element is disposed on a first catheter which is inserted into the vena cava from below the junctions of the vena cava with the subject's renal veins (e.g., via the subject's femoral vein), and the downstream blood pump is disposed on a second catheter, which inserted into the vena cava from above the junctions of the vena cava with the subject's renal veins (e.g., via the subject's subclavian vein, or jugular vein).
  • an occlusion element such as a balloon 80 ( Fig. 5A ), covered frame 82 ( Fig. 5B ), or a nozzle (not shown, e.g., as described in co-pending PCT Patent Application No. PCT/IL2017/051092 to Tuval, filed Sep. 28, 2017 , which is incorporated herein by reference) is used instead of an upstream impeller, such that the blood flow that impacts the downstream impeller is not undergoing rotational motion in the same direction as the downstream impeller.
  • an occlusion element is placed within the vena cava upstream of junctions of the vena cava with all of the renal veins even in the absence of a downstream blood pump, for example, as described in further detail hereinbelow with reference to Fig. 22A .
  • FIG. 6 is a schematic illustration of blood-pump catheter 20 placed within a subject's vena cava 22, upstream pump 24U being disposed upon the catheter, distally to downstream pump 24D, and a support stent 160 being disposed upon the catheter between the upstream and downstream pumps, in accordance with some applications of the present invention.
  • upstream pump 24U being disposed upon the catheter
  • downstream pump 24D distally to downstream pump 24D
  • a support stent 160 being disposed upon the catheter between the upstream and downstream pumps
  • stent 160 is configured to support the walls of the vena cava at the low-pressure region, such that the vena cava does not become obstructed at the low-pressure region, due to the walls of the vena cava collapsing. For example, if, due to the pumping of the upstream and downstream pumps, the pressure within the vena cava in the region between the pumps falls below the subject's intraabdominal pressure, then the walls of the vena cava may collapse in the absence of a support structure, such as support stent 160.
  • stent 160 has a generally similar shape to cage 30.
  • Fig. 6 shows stent 160 disposed upon a blood-pump catheter, upon which the upstream pump is disposed distally to the downstream pump, for some applications, stent 160 is disposed upon a blood-pump catheter, upon which the downstream pump is disposed distally to the upstream pump, as described hereinabove.
  • Fig. 6 shows stent 160 disposed upon a blood-pump catheter, upon which the upstream pump is disposed distally to the downstream pump, for some applications, stent 160 is disposed upon a blood-pump catheter upon which an occlusion element and a downstream pump are disposed, e.g., as shown in Figs. 5A-B .
  • FIGS. 7A , 7B , 7C , 7D , and 7E are schematic illustrations of blood-pump catheter 20 placed within a subject's vena cava 22, upstream impeller 28U being disposed upon the catheter, distally to downstream impeller 28D, the upstream and downstream impellers being disposed within a support cage 170 that supports the walls of a portion of the vena cava between the upstream and downstream impellers, in accordance with some applications of the present invention.
  • FIG. 7A-E shows support cage 170 disposed upon a blood-pump catheter, upon which the upstream pump is disposed distally to the downstream pump, for some applications, support cage 170 is disposed upon a blood-pump catheter, upon which the downstream pump is disposed distally to the upstream pump, as described hereinabove.
  • Figs. 7A-E shows support cage 170 disposed upon a blood-pump catheter, upon which the upstream pump is disposed distally to the downstream pump, for some applications, support cage 170 is disposed upon a blood-pump catheter upon which an occlusion element and a downstream pump are disposed, e.g., as shown in Figs. 5A-B .
  • support cage 170 is configured to support the walls of the vena cava at the low-pressure region, such that the vena cava does not become obstructed at the low-pressure region, due to the walls of the vena cava collapsing. For example, if, due to the pumping of the upstream and downstream pumps, the pressure within the vena cava in the region between the pumps falls below the subject's intraabdominal pressure, then the walls of the vena cava may collapse in the absence of a support structure, such as support cage 170.
  • the support cage is radially expandable and is shape to assume a radially expanded configuration thereof in the absence of any radially constraining force acting upon the support cage.
  • the support cage may be made of a shape memory material, e.g., a shape memory metal or alloy (such as, nitinol).
  • the support cage is configured to extend longitudinally along more than 50 percent of a region between the first and second impellers, the support cage being configured to thereby support the inner wall of the vena cava in an open configuration in the region between the first and second impellers.
  • support cage is configured to extend at least from the longitudinal center of the downstream impeller to the longitudinal center of the upstream impeller.
  • a length L1 ( Fig.
  • a diameter D3 ( Fig. 7B ) of support cage 170, when the cage is in a substantially non-constrained configuration thereof inside the vena cava, is more than 14 mm (e.g., more than 16 mm), and/or less than 35 mm (e.g., less than 25 mm), e.g., 14-35 mm, or 16-25 mm.
  • the support cage may be somewhat radially constrained when disposed within the vena cava due to radial compression of the walls of the vena cava upon the support cage.
  • the impellers are placed inside support cage 170, in the absence of individual cages that are disposed around the respective impellers.
  • the support cage is typically configured to (a) support the walls of the vena cava at the low-pressure region, as described hereinabove, and (b) to maintain a separation between the impellers and the inner wall of the vena cava, in a generally similar manner to that described hereinabove with respect to cage 30.
  • Fig. 7A shows a blood-pump catheter as described, placed inside the subject's vena cava 22.
  • Fig. 7B shows a three-dimensional view of impellers and support cage 170 as described, in the absence of the subject's anatomy.
  • Fig. 7C shows a three-dimensional view of impellers and support cage 170, in the absence of the subject's anatomy, and with the support cage including support elements 172, in accordance with some applications of the present invention.
  • an axial shaft 51 is disposed between the proximal and distal impellers and is configured to impart rotational motion from the proximal impeller to the distal impeller.
  • support elements 172 extend from the support cage, and are coupled to axial shaft 51, such as to maintain the disposition of shaft 51 along the longitudinal axis of the support cage. In this manner, the disposition of the axial shaft is typically maintained along the longitudinal axis of the vena cava. Further typically, the support elements maintain the longitudinal axes of the proximal and distal impellers in alignment with one another, and in alignment with the longitudinal axis of the vena cava.
  • impellers 28D and 28U are placed inside support cage 170, in the presence of individual cages that are disposed around the respective impellers.
  • the individual cages in which the impellers are disposed are generally similar to impeller cage 30, as described hereinabove.
  • support cage 170 is shaped to define individual impeller cages 174, one or more of which are formed as a single integrated structure together with the support cage, as shown in Fig. 7D .
  • one or more of the individual impeller cages and the support cage may be cut from a single piece of a shape memory metal or alloy (e.g., nitinol) using techniques as described hereinbelow with reference to Figs. 11A-C .
  • a shape memory metal or alloy e.g., nitinol
  • individual impeller cages 30 may be formed separately from support cage 170, as shown in Fig. 7E .
  • the impellers may be placed inside individual impeller cages 30, as described hereinabove, and individual impeller cages 30 may then be placed inside support cage 170.
  • individual impeller cages 30 are placed inside support cage 170 inside the subject's body (e.g., inside the subject's vena cava).
  • individual impeller cages 30 are placed inside support cage 170 outside the subject's body (e.g., within guide catheter 23, shown in Fig. 1A ), and the individual impeller cages are deployed inside the subject's body (e.g., inside the subject's vena cava) together with the support cage.
  • Figs. 6 and Figs. 7A-E show examples of blood-pump catheter 20 in which the blood-pump catheter includes a support structure (e.g., stent 160, or support cage 170), a longitudinal center of the support structure being disposed between the upstream and downstream blood pumps (e.g., between the upstream and downstream impellers).
  • the longitudinal center of the support structure is disposed equidistantly from the upstream and downstream blood pumps (e.g., the upstream and downstream impellers).
  • the support structure is configured to support an inner wall of the vena cava in an open configuration during the pumping of the blood by the first and second pumps.
  • a support structure such as the structure shown in Figs.
  • a blood-pump catheter that includes a downstream pump and an upstream occlusion element (e.g., as shown in Figs. 5A-B ), mutatis mutandis.
  • the support structure is configured to support an inner wall of the vena cava in an open configuration during the pumping of the blood by the downstream pump.
  • FIGs. 8A , 8B , and 8C are graphs showing the pressure drop recorded in models of a subject's left and right renal veins, during experiments that were conducted using pumps, in accordance with some applications of the present invention.
  • a model of the vena cava and renal veins was used.
  • the model was made of flexible silicone filled with saline.
  • Upstream and downstream pumps as described herein were placed inside the vena cava, respectively below and above the renal veins.
  • the pumps were activated to pump the saline through the vena cava in the manner described herein, and the drop in pressure in left and right renal veins was measured relative to the pressure in the left and right renal veins before the pumps were activated.
  • Fig. 8A shows a plot of the measured pressure reduction (dP) in the left and right renal veins for respective rates of revolutions per minute (RPM) of the pumps (which was always the same for both pumps), for when the pumps were placed in the vena cava in the absence of either a support stent (as shown in Fig. 6 ) or a support cage or sleeve (as shown in Figs. 7A-E , 9A-B , 10A-D , and/or 11A-C ) between the upstream and downstream pumps.
  • RPM revolutions per minute
  • Fig. 8B shows a plot of the measured pressure reduction (dP) in the left and right renal veins for respective rates of revolutions per minute (RPM) of the pumps (which was always the same for both pumps), for when the pumps were placed in the vena cava in the presence of a support stent (as shown in Fig. 6 ) between the upstream and downstream pumps.
  • DP measured pressure reduction
  • RPM revolutions per minute
  • Fig. 8C shows a plot of the measured pressure reduction (dP) in the left and right renal veins for respective rates of revolutions per minute (RPM) of the pumps (which was always the same for both pumps), for when the pumps were placed in the vena cava in the presence of a support cage between the upstream and downstream pumps, the support cage being configured as shown in Fig. 7E .
  • the results shown in Figs. 8A-C indicate that the efficacy of the reducing renal venous pressure by pumping blood through the vena cava using upstream and downstream pumps as described herein may be improved by placing a support structure inside the vena cava between the upstream and downstream pumps, in accordance with techniques described herein. Furthermore, the results indicate that the efficacy of the aforementioned technique may be improved by placing a support cage inside the vena cava that extends at least from the longitudinal center of the downstream pump (e.g., the longitudinal center of the impeller of the downstream pump) to the longitudinal center of the upstream pump (e.g., longitudinal center of the impeller of the upstream pump). Therefore, for some applications of the present invention, apparatus and methods as described in Figs. 6 , 7A-E , 9A-B , 10A-D , and/or 11A-C are used.
  • FIGs. 9A-B are schematic illustrations of blood-pump catheter 20 for placing within a subject's vena cava 22, an upstream impeller 28U being disposed upon the catheter, proximally to a downstream impeller 28D, the upstream and downstream impellers being disposed within a support cage 180 that supports the walls of a portion of the vena cava between the upstream and downstream impellers, in accordance with some applications of the present invention.
  • Support cage 180 is typically generally similar to support cage 170 described hereinabove, except for the differences described hereinbelow.
  • impellers 28 are disposed inside respective impeller cages 30, and the impeller cages are not sized such as to hold open the inner wall of the vena cava under normal conditions, the diameter of the cages being less than that of the vena cava, as shown in Figs. 9A-B .
  • impeller cage 30 typically functions to separate the inner wall of the vena cava from the impeller, such that the vena cava does not become injured by the impeller, for example in case intra-abdominal pressure is exerted upon the vena cava, such that the vena cava collapses against the impeller cages.
  • the stiffness of cage 30 is sufficiently great that pressure exerted upon the cage by the inner wall of the vena cava does not deform the cage.
  • the cage thereby protects the impeller from being deformed by pressure from the inner wall of the vena cava.
  • support cage 180 is configured to extend longitudinally along more than 50 percent of a region between the first and second impellers, the support cage being configured to thereby support the inner wall of the vena cava in an open configuration in the region between the first and second impellers, e.g., as described hereinabove with reference to support cage 170.
  • support cage extends at least from the longitudinal center of the downstream impeller to the longitudinal center of the upstream impeller.
  • the support cage extends from the upstream end of the upstream impeller cage to the downstream end of the downstream impeller cage.
  • the dimensions of support cage 180 are generally similar to those described hereinabove with reference to support cage 170.
  • the maximum diameter of the support cage i.e., the diameter of the support cage at the longitudinal location(s) at which the diameter of the support cage is at its maximum
  • the maximum diameter of each of the impeller cages 30 i.e., the diameters of each of the impeller cages at the longitudinal location(s) at which the diameter of each of the impeller cages is at its maximum
  • the maximum diameter of the support cage is approximately 30 mm (e.g., 30 mm plus/minus 3 mm), and the maximum diameter of each of the impeller cages is approximately 20 mm (e.g., 20 mm plus/minus 3 mm).
  • the stiffness of each of the impeller cages is at least 1.5 times greater than the stiffness of the support cage.
  • the impeller cages are shape set such that the diameters of the impeller cages are less than that of the vena cava. Therefore, the cages are configured to be of sufficient stiffness not to be deformed by pressure from the vena cava walls.
  • the support cage is typically shape set such that the diameter of the support cage is greater than the diameter of the vena cava, at least in some subjects.
  • the support cage is typically configured to have a stiffness that is such that the support cage is at least partially narrowed by the vena cava in the event that the diameter of the support cage, in its non-constrained configuration, is greater than the diameter of the vena cava. It is noted that, even in such applications, the stiffness of the impeller cage is configured to permit the impeller cage to be inserted into the subject's vena cava by being crimped inside guide catheter 23, and to permit the impeller cage to navigate turns while being advanced through the guide catheter.
  • FIGs. 10A, 10B , 10C, and 10D are schematic illustrations of a support sleeve 190 having an open end 192, and impeller cages 30 for use therewith, in accordance with some applications of the present invention.
  • Support sleeve 190 is typically generally similar to support cage 170 described hereinabove, except for the differences described hereinbelow.
  • Support sleeve 190 (shown in Fig. 10A ) is typically used with upstream and downstream impellers 28 and impeller cages 30 (shown in Fig. 10B ), which are generally as described herein.
  • Fig. 10C shows the impeller cages disposed inside support sleeve 190, and Fig.
  • 10D shows the impeller cages disposed inside the support sleeve within vena cava 22.
  • one of the impeller cages and the corresponding impeller are able to pass through the open end of the support sleeve even when the impeller cage and corresponding impeller are in radially non-constrained configurations thereof.
  • the open end of the support sleeve is not fixedly coupled to the impeller cage and/or the impeller that is disposed toward the open end of the support sleeve.
  • support sleeve 190 is configured to be disposed around a first one of the impeller cages and to extend longitudinally along more than 50 percent of the region between the first and second impellers, the support sleeve being configured to thereby support the inner wall of the vena cava in an open configuration in the region between the first and second impellers, e.g., as described hereinabove with reference to support cage 170.
  • the support sleeve extends at least from the longitudinal center of the downstream impeller to the longitudinal center of the upstream impeller.
  • the support sleeve extends from the upstream end of the upstream impeller cage to the downstream end of the downstream impeller cage, e.g., as shown in Figs. 10C and 10D .
  • support sleeve 190 is released into the subject's vena cava prior to impellers 28 and impeller cages 30 being released into the vena cava. Subsequent to the support sleeve being released and radially expanding inside the vena cava, impellers 28 and impeller cages 30 are released into the vena cava.
  • support sleeve 190 is crimped inside guide catheter 23 without the impellers and the impeller cages disposed inside the support sleeve. Alternatively, the impellers and impeller cages are disposed inside the support sleeve when the support sleeve is crimped inside the guide catheter during insertion.
  • the open end of the support sleeve is not fixedly coupled to the impeller cage or to the impeller that are disposed toward the open end of the support sleeve.
  • the open end of the support sleeve is thereby able to move longitudinally with respect to the impeller cage and the impeller that are disposed toward the open end of the support sleeve, thereby allowing the support sleeve to become more longitudinally extended (e.g., during crimping) than if the end of the support sleeve were to be fixedly coupled to the impeller and/or to the impeller cage that are disposed toward the open end of the support sleeve.
  • FIGs. 11A , 11B, and 11C are schematic illustrations of an impeller cage 30 and a support sleeve 200 that are formed from a single tube of a shape-memory alloy (such as nitinol), and a cage assembly element 202 configured to hold closed one of the ends of the impeller cage, in accordance with some applications of the present invention.
  • Support sleeve 200 is typically generally similar to support cage 170 described hereinabove, except for the differences described hereinbelow.
  • an impeller cage 30 and support sleeve 200 are formed from a single tube of a shape-memory metal or alloy (such as nitinol), by cutting both the impeller cage and the support sleeve to have one open end. Subsequent to cutting the tube, the open end of the impeller cage is closed using a cage assembly element 202, which may, for example be a ring-shaped fastening element, as shown, and/or a clip, a suture, a tie, adhesive, etc.
  • a cage assembly element 202 which may, for example be a ring-shaped fastening element, as shown, and/or a clip, a suture, a tie, adhesive, etc.
  • the maximum diameter D4 ( Fig. 11B ) of the support sleeve i.e., the diameter of the support sleeve at the longitudinal location(s) at which the diameter of the support sleeve is at its maximum
  • a maximum diameter D5 ( Fig. 11B ) of the support sleeve is at least 1.1 times (and, for some applications, at least 1.3 times) greater than a maximum diameter D5 ( Fig.
  • each of the impeller cages 30 i.e., the diameters of each of the impeller cages at the longitudinal location(s) at which the diameter of each of the impeller cages is at its maximum
  • the maximum diameter of the support sleeve is approximately 30 mm (e.g., 30 mm plus/minus 3 mm)
  • the maximum diameter of each of the impeller cages is approximately 20 mm (e.g., 20 mm plus/minus 3 mm).
  • one of the impellers is fixedly coupled to the support sleeve, by virtue of the impeller and the support sleeve having been formed from a single tube of shape-memory alloy, as described hereinabove.
  • the support sleeve is open, and the open end of the support sleeve is not fixedly coupled to the impeller cage or to the impeller that are disposed toward the open end of the support sleeve.
  • the impeller cage and the impeller that are disposed toward the open end of the support sleeve are able to pass through the end of the support sleeve even when the impeller cage and the impeller are in radially non-constrained configurations thereof.
  • the impeller and impeller cage that are disposed toward the open end of the support sleeve are disposed inside the support sleeve when the support sleeve is crimped inside the guide catheter.
  • the open end of the support sleeve is typically not fixedly coupled to the impeller cage or to the impeller that are disposed toward the open end of the support sleeve.
  • the open end of the support sleeve is thereby able to move longitudinally with respect to the impeller cage and the impeller that are disposed toward the open end of the support sleeve, thereby allowing the support sleeve to become more longitudinally extended (e.g., during crimping) than if the end of the support sleeve were to be fixedly coupled to the impeller and/or to the impeller cage that are disposed toward the open end of the support sleeve.
  • support sleeve 200 is configured to extend longitudinally from the first impeller and impeller cage along more than 50 percent of the region between the first and second impellers, the support sleeve being configured to thereby support the inner wall of the vena cava in an open configuration in the region between the first and second impellers, e.g., as described hereinabove with reference to support cage 170.
  • the support sleeve extends at least from the longitudinal center of the downstream impeller to the longitudinal center of the upstream impeller.
  • the support sleeve is configured, such that when the support sleeve radially expands inside the vena cava, the support sleeve does not extend longitudinally to the second impeller cage, e.g., as shown in Fig. 11C .
  • blood pumps 24U and 24D the catheters upon which the blood pumps are disposed (e.g., blood-pump catheter 20, catheter 66, and catheter 68), and the occlusion elements described with reference to Figs. 5A-B , and other devices described herein, are generally described as being placed within the subject's vena cava, such that the upstream pump or the occlusion element is disposed upstream of junctions of the vena cava with the subject's renal veins, and the downstream pump is disposed downstream of the junctions of the vena cava with the subject's renal veins.
  • the scope of the present invention includes placing upstream pump 24U or the occlusion element in any main vein upstream of a tributary venous system, and placing downstream pump 24D downstream of said tributary venous system, and configuring the pump(s) (e.g., via the direction of rotation of impellers of the pumps, or the orientation of the pumps) to generate preferential flow from the tributaries into the main vein, mutatis mutandis.
  • the pump(s) could be used to generate flow from the subject's hepatic veins into the subject's vena cava, in order to increase perfusion of the subject's liver, mutatis mutandis.
  • the upstream pump or the occlusion element is placed within a main vein upstream of two or more tributary venous systems into the main vein (e.g., within the vena cava upstream of the renal venous system and the hepatic venous system).
  • the downstream pump is placed downstream of the two or more tributary venous systems.
  • the pump(s) are configured to generate preferential flow from both of the tributary venous systems into the main vein by pumping blood through the main vein, in the manner described herein.
  • upstream and downstream pumps 24U and 24D and blood-pump catheter 20 are placed within the subclavian vein or jugular vein at junctions of the vein with a lymph duct and are used to increase flow of lymphatic fluid from the lymph duct into the vein, using the techniques described herein, mutatis mutandis.
  • upstream pump 24U or the occlusion element is placed in a main vein upstream of a tributary venous system
  • downstream pump 24D is placed downstream of said tributary venous system
  • the pump(s) are configured (e.g., via the direction of rotation of impellers of the pumps, or the orientation of the pumps) to reduce flow from the tributaries into the main vein.
  • the blades of the downstream impeller are oriented such that, as the downstream impeller is rotated, the downstream impeller pumps in the upstream direction (toward the junction between the tributary system and the main vein).
  • the blades of the upstream impeller are oriented such that, as the upstream impeller is rotated, the upstream impeller pumps in the downstream direction (toward the junction between the tributary system and the main vein).
  • the upstream and downstream pumps 24U and 24D, the catheter(s) upon which the blood pumps are disposed e.g., blood-pump catheter 20, catheter 66, and catheter 68
  • the occlusion elements described with reference to Figs. 5A-B , and other devices described herein are placed within a main artery upstream and downstream of bifurcations of the artery with one or more branching arterial systems that branch from the main artery and supply a given organ, mutatis mutandis.
  • the upstream pump is typically configured to pump in the downstream direction (toward the bifurcations) and the downstream pump is configured to pump in the upstream direction (toward the bifurcations), such that blood flow into the branching arterial system is increased, thereby increasing perfusion of the organ.
  • the occlusion element is placed downstream of the bifurcations of the artery with the one or more arterial systems and is configured to partially occlude the artery downstream of the bifurcations.
  • the upstream pump may be placed in the subject's aorta upstream of the subject's renal arteries and the downstream pump may be placed in the subject's aorta downstream of the subject's renal arteries, the pumps acting to pump blood into the renal arteries and toward the subject's kidneys.
  • upstream and downstream pumps, and/or occlusion elements are placed on both the arterial and venous sides of the subject's body in order to increase perfusion of a given organ or set of organs, in the manner described herein.
  • FIG. 12 is a schematic illustration of impeller-based blood pumps 150 inserted into a subject's left and right renal veins 42 via the subject's subclavian vein 40, in accordance with some applications of the present invention.
  • each of the blood pumps includes a radially-expandable impeller 152 disposed inside a radially-expandable impeller cage 154.
  • the blood pumps are inserted into the left and right renal veins via respective catheters 155.
  • the blood pumps are inserted via a single catheter that passes from the venous access point to the subject's vena cava.
  • the blood pumps are inserted into the subject's renal veins, while the blood pumps are in radially constrained configurations inside the guide catheter(s), and are configured to assume substantially radially non-constrained configurations by being released from the guide catheter(s) inside the subject's renal veins.
  • the catheters are both inserted via subclavian vein 40, as shown.
  • the catheters are inserted via a different vein, e.g., the subject's femoral vein, and/or the subject's jugular vein.
  • blood pumps 150 are generally similar to blood pumps described in US 2016/0022890 to Schwammenthal , which is incorporated herein by reference, apart from differences described hereinbelow.
  • Blood pumps 150 are typically placed inside the subject's renal veins 42, and operated therein, in order to provide acute treatment of a subject suffering from cardiac dysfunction, congestive heart failure, low renal blood flow, high renal vascular resistance, arterial hypertension, diabetes, and/or kidney dysfunction.
  • the therapeutic effect of operating blood pumps 150 within the renal veins (a) is typically generally similar to that described hereinabove with reference to blood-pump catheter 20, mutatis mutandis, and (b) is typically generally similar to the effect of renal vein blood pumps, as described in US 2016/0022890 to Schwammenthal , which is incorporated herein by reference.
  • the impellers of the blood pumps 150 are coupled to motors 232, which impart rotational motion to the impellers.
  • the motors are disposed outside of the subject's body (as shown) or are placed inside the subject's body (not shown).
  • a control unit 234 and a user interface 236 are disposed outside the subject's body. Further typically, the control unit receives inputs from pressure sensors, which are disposed on upstream and downstream sides of the blood pumps.
  • the pressure measured by the upstream pressure sensor is indicative of blood pressure upstream of the blood pump, inside the renal vein, and the pressure measured by a downstream pressure sensor is indicative of central venous pressure.
  • the control unit receives an input from an additional sensor (such as a flow sensor and/or an oxygen-saturation sensor, and/or a thermal flow sensor, e.g., as described with reference to Figs. 22Ai-22C ii of US 2016/0022890 to Schwammenthal , which is incorporated herein by reference), and the control unit controls the speed of the rotation of the impellers responsively to an input from the additional sensor.
  • an additional sensor such as a flow sensor and/or an oxygen-saturation sensor, and/or a thermal flow sensor, e.g., as described with reference to Figs. 22Ai-22C ii of US 2016/0022890 to Schwammenthal , which is incorporated herein by reference
  • control unit 234 controls rotation of impellers 152, by controlling motors 232, responsively to one or more of the above-described inputs.
  • user interface 236 displays the subject's current renal venous pressure and central venous pressure, based upon the pressures measured by the sensors.
  • a user such as a healthcare professional inputs a target value for the subject renal venous pressure, via the user interface.
  • control unit 234 controls the speed of the rotation of the impeller, such that the impeller pumps through the renal vein and toward the vena cava at a flow rate that is such as to reduce the renal venous pressure toward the target level, as indicated by the user.
  • control unit stops the impeller rotating.
  • the control unit typically controls the speed of the rotation of the impellers responsively to inputs from the upstream and downstream pressure sensors.
  • control unit 234 typically includes a computer processor that comprises circuitry and that is configured to execute the actions described herein. Typically, the operations described herein that are performed by the computer processor transform the physical state of a memory, which is a real physical article that is in communication with the computer processor, to have a different magnetic polarity, electrical charge, or the like, depending on the technology of the memory that is used.
  • Control unit 234 is typically a hardware device programmed with computer program instructions to produce a special-purpose computer. For example, when programmed to perform the techniques described herein, control unit 234 typically acts as a special-purpose, renal-venous-pressure-modulating computer processor.
  • user interface 236 typically includes any type of user interface configured to receive inputs from a user and/or to provide outputs to the user.
  • the user interface may include one or more input devices (such as a keyboard, a mouse, a trackball, a joystick, a touchscreen monitor, a touchpad, a voice-command interface, a smartphone, a tablet computer, and/or other types of input devices that are known in the art), and/or one or more output devices (such as a monitor, an audio output device, a smartphone, a tablet computer, and/or other types of output devices that are known in the art).
  • input devices such as a keyboard, a mouse, a trackball, a joystick, a touchscreen monitor, a touchpad, a voice-command interface, a smartphone, a tablet computer, and/or other types of input devices that are known in the art
  • output devices such as a monitor, an audio output device, a smartphone, a tablet computer, and/or other types of output devices that are known in the art.
  • Figs. 13A-B are schematic illustrations of impeller cage 154, the cage including radially-protruding support arms 156 that are configured to align the longitudinal axis of impeller 152 with a local longitudinal axis of renal vein 42, in accordance with some applications of the present invention.
  • Fig. 13A shows the impeller cage disposed inside the subject's renal vein 42.
  • the impeller cage is sized such that, when the cage is in a radially non-constrained configuration, the maximum diameter of the cage (i.e., the diameter of the cage at the longitudinal location at which the diameter of the cage is at its maximum) is less than the diameter of the renal vein at the location within the renal vein at which the impeller cage is deployed, at least in some subjects.
  • diameters of renal veins vary from approximately 8 mm to approximately 16 mm, and, for example, the diameter of the impeller cage may be more than 8 mm (e.g., more than 10 mm), and/ or less than 13 mm (e.g., less than 12 mm), e.g., between 8 and 13 mm, or between 10 and 12 mm.
  • the cage is typically configured to have a stiffness that is such that even if pressure is exerted upon the cage by walls of the renal vein, the cage does not become deformed, and the cage thereby protects the impeller from becoming deformed.
  • impeller cages for placement within the renal veins as described herein are configured to be have diameters that are substantially greater than the diameters of some subjects' renal veins, and the impeller cages are configured to become radially compressed by the walls of the renal veins, this may result in the impeller becoming deformed (e.g., by the upstream and downstream ends of the impeller axis becoming misaligned), and/or in the impeller becoming misaligned with the local longitudinal axis of the renal veins.
  • the impeller cage is configured to have a smaller diameter, such that even in cases in which the impeller cage has a greater diameter than a subject's renal vein (e.g., in the case of a subject with narrow renal veins), the radial force that is exerted upon the impeller cage by the subject's renal vein is lower.
  • the impeller cage is configured to have a stiffness that is such that even if pressure is exerted upon the cage by walls of the renal vein, the cage does not become deformed, and the cage thereby protects the impeller from becoming deformed.
  • the stiffness of the impeller cage is configured to permit the impeller cage to be inserted into the subject's renal vein by being crimped inside guide catheter 155, and to permit the impeller cage to navigate turns while being advanced through the guide catheter.
  • impeller cage 154 is configured such that the maximum diameter of the cage is less than the diameter of the renal vein at the location within the renal vein at which the impeller cage is deployed.
  • radially-protruding support arms 156 protrude radially from the impeller cage.
  • the radially-protruding support arms 156 are configured, upon the blood pump being released into the subject's renal vein, to come into contact with the inner wall of the subject's renal vein by radially expanding.
  • the radially-protruding support arms 156 are configured to thereby align the longitudinal axis of impeller 152 with a local longitudinal axis of renal vein 42, as shown in Fig. 13A .
  • the efficacy of the pumping of blood by impeller 152 is greater, the greater than alignment of the longitudinal axis of the impeller with the local longitudinal axis of the renal vein.
  • the radially-protruding support arms may not fully align the longitudinal axis of impeller with the local longitudinal axis of renal vein.
  • the radially-protruding support arms maintain the longitudinal axis of the impeller in greater alignment with the local longitudinal axis of the renal vein, relative to alignment of the longitudinal axis of the impeller with the local longitudinal axis of the renal vein in the absence of the support arms, ceteris paribus.
  • the radially-protruding support arms each define a radius R1 with respect to the longitudinal axis 153 of the shaft of the blood pump that is greater than 7 mm and/or less than 9 mm, e.g., 7-9 mm.
  • Radius R1 (shown in Fig. 13B ) is a measure of the maximum radial distance between the support arm and longitudinal axis 153.
  • cage 30 defines a bulbous extension that, for example, may be generally similar in shape to bulbous extension 84 described hereinbelow with reference to Fig. 16 , mutatis mutandis.
  • control unit 234 receives inputs from pressure sensors that are disposed on upstream and downstream sides of the blood pumps, and controls rotation of impellers 152, by controlling motors 232, responsively to one or more of the inputs.
  • upstream pressure sensor 158 is disposed on the shaft of blood pump 150 distally to the impeller and the impeller cage. If the upstream pressure sensor comes into contact with the inner wall of the renal vein, then the upstream pressure sensor may measure the subject's intraabdominal pressure, which is conveyed through the wall of the renal vein, as opposed to measuring blood pressure within the renal vein.
  • radially-protruding support arms 156 are configured to separate the upstream pressure sensor from the inner wall of the renal vein, by centering the shaft of the blood pump within the renal vein.
  • the radially-protruding support arms may maintain the pressure sensor at a distance of at least 2 mm from an inner wall of the renal vein.
  • the impeller cage is sized such that, when the cage is in its radially non-constrained configuration, the maximum diameter of the cage is less than the diameter of the renal vein, as described hereinabove.
  • the longitudinal axis of the impeller is maintained substantially in alignment with the local longitudinal axis of the renal vein by guide catheter 155 providing support to the impeller and the impeller cage.
  • the guide catheter may be inserted into the renal vein via the subject's femoral vein, and the catheter may be configured as described in US 2015/0157777 to Tuval , which is incorporated herein by reference.
  • the guide catheter is typically configured to maintain pressure sensor 158 at a distance of at least 2 mm from an inner wall of the blood vessel, as described hereinabove.
  • control unit 124 is configured to account for pressure sensor 158 contacting the inner wall of the renal vein, and measuring the subject's intraabdominal pressure.
  • control unit may run the following algorithm:
  • control unit 52 ( Fig. 1 ), in order to accurately measure blood pressure within the subject's vena cava and/or renal veins, mutatis mutandis.
  • Fig. 14 is a schematic illustration of pressure sensor 158 disposed on a shaft 161 of impeller-based blood pump 150, in accordance with some applications of the present invention.
  • the distal portion of shaft 161 defines an indentation 163 therein.
  • Pressure sensor 158 is disposed inside the indentation.
  • pressure sensor is disposed inside indentation 163, so as to reduce the likelihood of the pressure sensor coming into contact with the wall of the renal vein.
  • Fig. 15 is a schematic illustration of a blood pump 210 configured to pump blood from a subject's right atrium 212 into the subject's coronary sinus 214, in accordance with some applications of the present invention.
  • blood pump 210 is an impeller-based pump that is generally similar to pump 150 described hereinabove.
  • blood pump 210 may have a different configuration.
  • the blood pump is inserted into the subject's right atrium and/or coronary sinus via the subject's vena cava, e.g., from a venous access point that is in the subject's femoral vein, subclavian vein, and/or jugular vein.
  • Blood pump 210 is configured to pump blood in a retrograde direction, from the subject's right atrium into the subject's coronary sinus.
  • the blood pump is configured to increase blood pressure in the coronary sinus, and to thereby increase blood pressure within the capillary system, from which blood flows indirectly into the coronary sinus. This, in turn, increases blood supply to the myocardium.
  • perfusion to vascular beds that are distal to the coronary obstruction is increased.
  • the level of oxygenation of blood in the coronary sinus (which is, typically, approximately 40 percent) is typically lower than that of blood entering to the right atrium from the vena cava (which is, typically, approximately 60-70 percent).
  • the blood pump is configured to pump, into the coronary sinus, blood that has returned to the right atrium from the vena cava, thereby increasing the level of oxygenation of the blood in the coronary sinus. This, in turn, increases the level of oxygenation of blood within the capillary system, from which blood flows indirectly into the coronary sinus.
  • blood pump 210 both (a) increases blood pressure within the coronary sinus, and (b) increases the level of oxygenation of blood within the coronary sinus.
  • Fig. 16 is a schematic illustration of a catheter that includes downstream pump 24D and balloon 80, in accordance with some applications of the present invention.
  • the apparatus shown in Fig. 16 is generally similar to that shown in Fig. 5A , except for differences described hereinbelow.
  • the apparatus includes a catheter 20, which includes downstream pump 24D and an occlusion element, such as balloon 80, as shown.
  • a nozzle is used as the upstream occlusion element, e.g., as described in co-pending PCT Patent Application No. PCT/IL2017/051092 to Tuval, filed Sep. 28, 2017 , which is incorporated herein by reference.
  • downstream pump is placed inside vena cava 22, downstream of the junctions of the vena cava with all of the subject's renal veins.
  • the downstream pump pumps blood through the vena cava, in the downstream direction, away from the junctions of the vena cava with the renal veins, in the manner described hereinabove.
  • the occlusion element is placed inside the vena cava upstream of the junctions of the vena cava with the subject's renal veins.
  • the occlusion element is configured to partially occlude the subject's vena cava upstream of the junctions of the vena cava with the subject's renal veins.
  • the occlusion element is configured to partially occlude the subject's vena cava such that, in response to the pumping of the downstream blood pump, there is not a substantial increase of blood flow from the subject's lower body toward the subject heart, but such that a region of low pressure within the vena cava is generated, between the occlusion element and the downstream blood pump, within which the blood pressure is lower than the subject's central venous pressure.
  • a region of low pressure blood flow from the renal veins into the vena cava increases, thereby lowering renal blood pressure and enhancing renal perfusion.
  • the occlusion element is configured to partially occlude, but not to totally occlude, the vena cava, in such a manner as to generate a region of low pressure within the vena cava, but to allow a substantial flow of blood through the vena cava.
  • impeller 28 of blood pump 24D is disposed inside impeller cage 30, and the impeller cage is not sized such as to hold open the inner wall of the vena cava, the diameter of the cage being less than that of the vena cava under normal conditions, as shown in Fig. 17 .
  • impeller cage 30 has a generally similar configuration to that described hereinabove with reference to Figs. 9A-B .
  • impeller cage 30 typically functions to separate the inner wall of the vena cava from the impeller, e.g., in case the vena cava collapses inwardly due to intra-abdominal pressure, such that the vena cava does not become injured by the impeller and the impeller does not become deformed by pressure from the inner wall of the vena cava.
  • the stiffness of impeller cage 30 is sufficiently great that pressure exerted upon the cage by the inner wall of the vena cava does not deform the cage.
  • a bulbous extension 84 that is configured to come into contact with the inner wall of the vena cava extends from impeller cage 30.
  • Bulbous extension 84 is configured to align the longitudinal axis of cage 30, and, in turn, impeller 28, with the local longitudinal axis of the vena cava, by contacting the inner wall of the vena cava.
  • the bulbous extension may not fully align the longitudinal axis of impeller with the local longitudinal axis of the vena cava.
  • the bulbous extension maintains the longitudinal axis of the impeller in greater alignment with the local longitudinal axis of the vena cava, relative to alignment of the longitudinal axis of the impeller with the local longitudinal axis of the vena cava in the absence of the bulbous extension.
  • the efficacy of the pumping of blood by impeller 28 is greater, the greater than alignment of the longitudinal axis of the impeller with the local longitudinal axis of the vena cava.
  • the bulbous extension is configured to prevent a pressure sensor that is coupled to blood pump 24D from coming into contact with the inner wall of the vena cava, and to thereby prevent the pressure sensor from measuring the subject's intraabdominal pressure instead of measuring blood pressure within the subject's vena cava, in a generally similar manner to that described hereinabove with reference to Figs. 13A-B .
  • the maximum diameter of bulbous extension 84 i.e., the diameter of the bulbous extension at the longitudinal location(s) at which the diameter of the bulbous extension is at its maximum
  • the maximum diameter of impeller cage 30 i.e., the diameters of the impeller cage at the longitudinal location(s) at which the diameter of the impeller cage is at its maximum
  • cage 30 defines radially-protruding support arms that are generally similar to radially-protruding support arms described hereinabove with reference to Figs. 13A-B , mutatis mutandis.
  • the scope of the present invention includes using any radially-protruding extension from an impeller cage that is, in at least some subjects, undersized with respect to a blood vessel in which the impeller cage is being placed, in order to maintain the longitudinal axis of an impeller (within the impeller cage) in greater alignment with the local longitudinal axis of the blood vessel, relative to alignment of the longitudinal axis of the impeller with the local longitudinal axis of the blood vessel in the absence of the radially-protruding extension.
  • the radially-protruding extension may be a bulbous extension (e.g., as shown in Fig. 16 ), or radially-protruding support arms (e.g., as shown in Fig. 13A ).
  • the blood vessel may include the vena cava (e.g., as shown in Fig. 16 ), or a renal vein (e.g., as shown in Fig. 13A ).
  • such a catheter which includes a downstream pump 24D disposed distally with respect to an occlusion element 80 is suitable for placement into the vena cava from a vein that is below the junctions of the vena cava with the subject's renal veins, e.g., the femoral vein (e.g., using a generally similar technique to that described hereinabove, with reference to Fig. 4 , mutatis mutandis ).
  • the scope of the present invention includes a catheter that has a pump and an occlusion element disposed thereon, but with the upstream occlusion element disposed distally with respect to the downstream pump.
  • Such a catheter is typically inserted via a vein that is disposed above the inferior vena cava, e.g., the subclavian vein or the jugular vein, e.g., using generally similar techniques to those described hereinabove, with reference to Figs. 1 and 3 , mutatis mutandis.
  • a vein that is disposed above the inferior vena cava, e.g., the subclavian vein or the jugular vein, e.g., using generally similar techniques to those described hereinabove, with reference to Figs. 1 and 3 , mutatis mutandis.
  • FIG. 17 is a schematic illustration of apparatus that was used in an experiment performed in accordance with some applications of the present invention.
  • a blood-pump catheter, generally as described with reference to Fig. 16 was placed inside the vena cava of a pig weighing 66 kg.
  • Pressure sensors 86L and 86R were placed inside the pig's left and right renal veins in order to measure renal venous pressure.
  • a pressure sensor 88 was disposed on the shaft of the blood-pump catheter between balloon 80 and the downstream blood pump 24D.
  • An additional balloon 90 was inserted into the pig's vena cava, downstream of the downstream blood pump. The additional balloon was inflated in order to increase the pig's central venous pressure, in order to mimic a subject suffering from high central venous pressure.
  • the pig initially had central venous pressure of 10 mmHg.
  • the pig's central venous pressure was raised to 20 mmHg, by inflating balloon 90.
  • Pumping of blood by the downstream blood pump was then initiated and the venous pressure as measured by pressure sensors 86L, 86R and 88 were recorded, while the rotation speed of the impeller of blood pump 24D was increased.
  • Fig. 18 is a graph showing the results of the experiment that was performed in accordance with some applications of the present invention.
  • the graph shows plots of the renal venous pressure as measured by (a) left renal vein pressure sensor 86L (indicated by “RVP-LEFT” in the legend on the graph), (b) right renal vein pressure sensor 86L (indicated by “RVP-RIGHT” in the legend on the graph), and (c) pressure sensor 88, disposed on the shaft of the blood-pump catheter (indicated by "RVP-CENTRAL” in the legend on the graph), plotted against revolutions per minute (RPM) of the impeller of blood pump 24D.
  • RPM revolutions per minute
  • Figs. 19A and 19B are schematic illustrations of blood pump 24, in accordance with some applications of the present invention.
  • the blood pump as shown in Figs. 19A and 19B is used in a generally similar manner to that shown in Fig. 16 . That is, blood pump 24 is disposed at the distal end of a catheter, and an occlusion element (e.g., balloon 80, as shown in Fig. 16 ) is disposed proximally to the blood pump.
  • the pump is placed inside vena cava 22, downstream of the junctions of the vena cava with all of the subject's renal veins.
  • the pump pumps blood through the vena cava, in the downstream direction, away from the junctions of the vena cava with the renal veins, in the manner described hereinabove.
  • the occlusion element is placed inside the vena cava upstream of the junctions of the vena cava with the subject's renal veins.
  • the occlusion element is configured to partially occlude the subject's vena cava upstream of the junctions of the vena cava with the subject's renal veins.
  • the occlusion element is configured to partially occlude the subject's vena cava such that, in response to the pumping of the blood pump, there is not a substantial increase of blood flow from the subject's lower body toward the subject heart, but such that a region of low pressure within the vena cava is generated, between the occlusion element and the downstream blood pump, within which the blood pressure is lower than the subject's central venous pressure.
  • a region of low pressure blood flow from the renal veins into the vena cava increases, thereby lowering renal blood pressure and enhancing renal perfusion.
  • the occlusion element is configured to partially occlude, but not to totally occlude, the vena cava, in such a manner as to generate a region of low pressure within the vena cava, but to allow a substantial flow of blood through the vena cava.
  • a catheter which includes pump 24 that is typically disposed distally with respect to an upstream occlusion element, is suitable for placement into the vena cava from a vein that is below the junctions of the vena cava with the subject's renal veins, e.g., the femoral vein (e.g., using a generally similar technique to that described hereinabove, with reference to Fig. 4 , mutatis mutandis ).
  • the scope of the present invention includes a catheter that has a pump and an occlusion element disposed thereon, but with the upstream occlusion element disposed distally with respect to the downstream pump.
  • Such a catheter is typically inserted via a vein that is disposed above the inferior vena cava, e.g., the subclavian vein or the jugular vein, e.g., using generally similar techniques to those described hereinabove, with reference to Figs. 1 and 3 , mutatis mutandis.
  • a vein that is disposed above the inferior vena cava, e.g., the subclavian vein or the jugular vein, e.g., using generally similar techniques to those described hereinabove, with reference to Figs. 1 and 3 , mutatis mutandis.
  • Fig. 19D is a schematic illustration of impeller 28 of blood pump 24, in accordance with some applications of the present invention.
  • blood pump 24 includes impeller 28, and the distal end of the impeller is not coupled to a distal bearing.
  • the distal end of the impeller is typically substantially maintained in alignment with a proximal end of the impeller, by virtue of a frame 250 of the impeller being of sufficient stiffness.
  • the frame of the impeller includes a plurality of helical elongate elements 252, which support a film 253 of a material (e.g., silicone) therebetween.
  • the impeller may be generally as described in US 2016/0022890 to Schwammenthal , which is incorporated herein by reference.
  • impeller 28 is disposed inside a support cage 254, the support cage including a narrow proximal portion 256, in which the impeller is configured to be disposed, during use of blood pump 24.
  • Proximal portion 256 typically functions to separate the inner wall of the vena cava from the impeller (e.g., in case the vena cava collapses inwardly due to intra-abdominal pressure), such that the vena cava does not become injured by the impeller and the impeller does not become deformed by pressure from the inner wall of the vena cava.
  • the stiffness of proximal portion 256 is sufficiently great that pressure exerted upon the proximal portion of the support cage by the inner wall of the vena cava does not deform the proximal portion of the support cage.
  • a bulbous distal extension 258 of the support cage extends from proximal portion 256 of the support cage, and is configured to come into contact with the inner wall of the vena cava.
  • Bulbous distal extension 258 is configured to align the longitudinal axis of support cage 254, and, in turn, impeller 28, with the local longitudinal axis of the vena cava, by contacting the inner wall of the vena cava.
  • the bulbous distal extension may not fully align the longitudinal axis of impeller with the local longitudinal axis of the vena cava.
  • the bulbous distal extension maintains the longitudinal axis of the impeller in greater alignment with the local longitudinal axis of the vena cava, relative to alignment of the longitudinal axis of the impeller with the local longitudinal axis of the vena cava in the absence of the bulbous extension.
  • the efficacy of the pumping of blood by impeller 28 is greater, the greater than alignment of the longitudinal axis of the impeller with the local longitudinal axis of the vena cava.
  • bulbous distal extension 258 of support cage 254 is configured to prevent a pressure sensor 259 that is coupled to blood pump 24 from coming into contact with the inner wall of the vena cava, and to thereby prevent the pressure sensor from measuring the subject's intraabdominal pressure instead of measuring blood pressure within the subject's vena cava, in a generally similar manner to that described hereinabove with reference to Figs. 13A-B .
  • the maximum diameter of bulbous distal extension 258 (i.e., the diameter of the bulbous distal extension at the longitudinal location(s) at which the diameter of the bulbous distal extension is at its maximum), when the bulbous distal extension is in a radially non-constrained configuration thereof, is at least 1.1 times (and, for some applications, at least 1.3 times) greater than the maximum diameter of proximal portion 256 of support cage 254 (i.e., the diameter of the proximal portion at the longitudinal location(s) at which the diameter of the proximal portion is at its maximum) when the proximal portion is in a radially non-constrained configuration thereof.
  • support cage 254 includes a frame 260 (e.g., a rigid or semi-rigid frame) made of a shape-memory element (such as nitinol) that is at least partially covered with a material 262 (e.g., a blood-impermeable material, e.g., polyester, polyurethane, and/or a different polymer).
  • a material 262 e.g., a blood-impermeable material, e.g., polyester, polyurethane, and/or a different polymer.
  • the material is coupled to the frame such as to contact the vessel wall and to occlude the blood vessel in the region of the blood vessel that surrounds the impeller.
  • the material typically defines a hole therethrough in a central region of the vessel in a vicinity of the impeller.
  • the material is configured to occlude backflow of blood around the outside of the impeller, but such to allow antegrade blood flow in the central region of the vessel in the vicinity of the impeller.
  • the use of the material in the above-described manner reduces a likelihood of there being retrograde blood flow in the region of the blood vessel that surrounds the impeller, caused by turbulence that is introduced by the impeller.
  • blood pump 24 as shown in Fig. 16 includes material that is coupled to cage 30 and/or bulbous extension 84, and that is configured to act in a generally similar manner to that described with reference to material 262.
  • support cage 254 defines radially-protruding support arms that are generally similar to radially-protruding support arms described hereinabove with reference to Figs. 13A-B , mutatis mutandis.
  • FIG. 19C shows relative dispositions into which impeller 28 and support cage 254 are placed prior to crimping the impeller and the support cage, in accordance with some applications of the present invention.
  • Support cage 254 is typically shape-set such as to assume a radially expanded configuration thereof in the absence of any radially constraining force acting upon the support cage, the radially expanded configuration being as shown in Figs. 19A-B .
  • the support cage is inserted into the subject's vena cava, while the support cage is in a radially constrained configuration (i.e., crimped) inside the guide catheter, and is configured to assume a substantially radially non-constrained configuration by being released from the guide catheter inside the subject's vena cava.
  • a radially constrained configuration i.e., crimped
  • a distal portion of support cage 254 is not covered with material 262. Furthermore, it is typically the case that, as shown, the spacing between struts of the frame of the support cage at its distal end is greater than at the proximal end of the support cage. Therefore, for some applications, in order to crimp the impeller inside the support cage, the impeller is first advanced to the distal portion of the support cage.
  • this allows for the combination of the impeller and the support cage to be crimped to a smaller diameter relative to if the impeller was disposed within the proximal portion of the support cage, since the impeller, by being disposed within the distal portion of the support cage, does not overlap with the material or with the portion of the support cage at which the struts of the support cage are closely spaced from each other. Further typically, this reduces the likelihood of the material and the impeller causing damage to one another during the crimping of the support cage and the impeller, relative to if the impeller was disposed within the proximal portion of the support cage.
  • the impeller is retracted with respect to the support cage, such that the impeller is disposed within the proximal portion of the support cage, as shown in Figs. 19A and 19B .
  • Figs. 20A and 20B are schematic illustrations of impeller 28 of blood pump 24, in accordance with some applications of the present invention.
  • blood pump 24 includes impeller 28, and the distal end of the impeller is not coupled to a distal bearing.
  • impeller 28 is as shown in Figs. 20A and 20B , the impeller including a plurality (e.g., two, three (as shown), or more than three) impeller blades 270, which are not directly connected with each other.
  • the impeller blades protrude in a petal-like manner from a proximal bearing 272.
  • Each of the blades typically includes a curved rigid or semi-rigid elongate element 274, which defines the outer edge of the blade and which extends from the proximal bearing from a first location around the circumference of the proximal bearing and curves back to a second location around the circumference of the proximal bearing.
  • the curved elongate element 274 typically supports a film of material 276 (e.g., silicone), the curved elongate element and the film of material defining the impeller blade.
  • impeller 28 as shown in Figs. 20A and 20B is configured such that more than 80 percent of the mass of the impeller is concentrated within the proximal-most 50 percent of the length of the impeller.
  • the relative concentration of the mass within the proximal-most 50 percent of the length of the impeller reduces vibration of the impeller during use of the impeller, relative to if more of the mass of the impeller was disposed within the distal-most 50 percent of the length of the impeller.
  • Figs. 21A and 21B are schematic illustrations of blood pump 24, the blood pump including impeller 28, impeller cage 30, and a frustoconical support cage 282, in accordance with some applications of the present invention.
  • Blood pump 24 is generally similar to that described hereinabove with reference to Fig. 16 , except for the differences described hereinbelow.
  • bulbous extension 84 as shown in Fig. 16
  • frustoconical support cage is used to align the longitudinal axis of cage 30, and, in turn, impeller 28, with the local longitudinal axis of the vena cava, by contacting the inner wall of the vena cava.
  • the frustoconical support cage typically extends from a location that is proximal to the impeller cage to a longitudinal location that is distal to the impeller cage, with the cage diverging in the proximal-to-distal direction.
  • the frustoconical support cage includes a frame 284 (e.g., a rigid or semi-rigid frame) made of a shape-memory element (such as nitinol) that is at least partially covered with a material 286 (e.g., a blood-impermeable material, e.g., polyester, polyurethane, and/or a different polymer).
  • Material 286 typically acts in a generally similar manner to that described with reference to material 262, described hereinabove with reference to Figs. 19A-C .
  • Frustoconical support cage 282 is typically shape-set such as to assume a radially expanded configuration thereof in the absence of any radially constraining force acting upon the support cage, the radially expanded configuration being as shown in Figs. 21A-B .
  • the frustoconical support cage is typically inserted into the subject's vena cava, while the support cage is in a radially constrained configuration (i.e., crimped) inside the guide catheter, and is configured to assume a substantially radially non-constrained configuration by being released from the guide catheter inside the subject's vena cava.
  • pump 24 is disposed upon a catheter distally with respect to an upstream occlusion element.
  • a catheter is suitable for placement into the vena cava from a vein that is below the junctions of the vena cava with the subject's renal veins, e.g., the femoral vein (e.g., using a generally similar technique to that described hereinabove, with reference to Fig. 4 , mutatis mutandis ).
  • the scope of the present invention includes a catheter that has a pump and an occlusion element disposed thereon, but with the upstream occlusion element disposed distally with respect to the downstream pump.
  • Such a catheter is typically inserted via a vein that is disposed above the inferior vena cava, e.g., the subclavian vein or the jugular vein, e.g., using generally similar techniques to those described hereinabove, with reference to Figs. 1 and 3 , mutatis mutandis.
  • a vein that is disposed above the inferior vena cava, e.g., the subclavian vein or the jugular vein, e.g., using generally similar techniques to those described hereinabove, with reference to Figs. 1 and 3 , mutatis mutandis.
  • the scope of the present invention includes any blood pump configured to be placed inside a blood vessel of a subject, and which includes (a) an impeller configured to pump blood by rotating, and (b) a support cage that is shaped to define (i) a narrow portion that is configured to be disposed around the impeller, and to maintain a separation between a wall of the blood vessel and the impeller, and (ii) a radial extension from the narrow portion of the support cage that extends radially outward with respect to the narrow portion of the support cage, the extension being configured to substantially maintain a longitudinal axis of the impeller in alignment with a local longitudinal axis of the blood vessel by contacting the wall of the blood vessel.
  • the narrow portion and the radial extension of the support cage are two separately-formed components.
  • the narrow portion and the radial extension of the support cage are two separately-formed components.
  • the narrow portion and the radial extension of the support cage are two separately-formed components.
  • the narrow portion and the radial extension of the support cage are two
  • an impeller that is undersized with respect to the vessel in which it is placed.
  • Such an impeller may be used, for example, in cases in which a larger impeller would undergo a substantial amount of vibration while rotating.
  • such an impeller may be used in cases in which, if the portion of the cage that is configured to separate between the impeller and the vessel wall was larger, there would be a risk that the portion of the cage would become radially compressed by the walls of the vessel, which may result in the impeller becoming deformed (e.g., by the upstream and downstream ends of the impeller axis becoming misaligned), and/or in the impeller becoming misaligned with the local longitudinal axis of the vessel.
  • a narrow portion of the cage surrounds the impeller and is configured to maintain a separation between a wall of the blood vessel and the impeller, for example, in case the vessel narrows, such that, in the absence of the narrow portion of the cage, the walls of the vessel would collapse onto the impeller.
  • the radial extension is typically configured to anchor the blood pump within the vessel by exerting an outward radial force upon the vessel wall, and to substantially maintain a longitudinal axis of the impeller in alignment with a local longitudinal axis of the blood vessel by contacting the wall of the blood vessel.
  • a stiffness of the narrow portion of the cage is greater than that of the radial extension, such that the narrow portion of the cage is configured to maintain the separation between the wall of the blood vessel and the impeller, even if the wall of the vessel exerts pressure upon the support cage that causes the radial extension to deform.
  • the blood pump includes impeller 28, cage 30, which constitutes a narrow portion of the overall support cage, and support cage 180, which constitutes a radial extension from the narrow portion of the cage.
  • the blood pump includes impeller 28, cage 30, which constitutes a narrow portion of the overall support cage, and support sleeve 190, which constitutes a radial extension from the narrow portion of the cage.
  • the blood pump includes impeller 28, cage 30, which constitutes a narrow portion of the overall support cage, and support sleeve 200, which constitutes a radial extension from the narrow portion of the cage.
  • the blood pump includes impeller 152, cage 154, which constitutes a narrow portion of the support cage, and radially-protruding support arms 156, which constitute radial extensions from the narrow portion of the cage.
  • the blood pump includes impeller 28, cage 30, which constitutes a narrow portion of the support cage, and bulbous extension 84, which constitutes a radial extension from the narrow portion of the cage.
  • the blood pump includes impeller 28, narrow proximal portion 256, which constitutes a narrow portion of the support cage 254, and bulbous distal extension 258, which constitutes a radial extension from the narrow portion of the cage.
  • the blood pump includes impeller 28, impeller cage 30, which constitutes a narrow portion of the support cage, and frustoconical support cage 282, which constitutes a radial extension from the narrow portion of the cage.
  • the radial extension extends from the narrow portion of the cage distally with respect to the narrow portion.
  • the radial extension extends from the narrow portion of the cage proximally with respect to the narrow portion, and/or level with the narrow portion.
  • a material e.g., blood-impermeable material
  • the support cage e.g., material 262, shown in Figs. 19A-B .
  • the material is coupled to the support cage such as to contact the vessel wall and to occlude the blood vessel in the region of the blood vessel that surrounds the impeller.
  • the material typically defines a hole therethrough in a central region of the vessel, in a vicinity of the impeller.
  • the material is configured to occlude backflow of blood around the outside of the impeller, but such as to allow antegrade blood flow in the central region of the vessel in the vicinity of the impeller.
  • such a blood pump is configured to be placed within a subject's renal vein and to pump blood from the subject's renal vein into the subject's vena cava, e.g., as described hereinabove with reference to Figs. 13A-B .
  • such a blood pump is configured to be placed within a subject's vena cava upstream of the junctions of the vena cava with all of the subject's renal veins, and to pump blood in a retrograde (i.e., upstream) direction, e.g., as described herein with reference to Fig. 22B .
  • such a blood pump is configured to be placed within a subject's vena cava downstream of the junctions of the vena cava with all of the subject's renal veins, and to pump blood in an antegrade (i.e., downstream) direction, e.g. as described herein with reference to Fig. 22C .
  • an occlusion element is configured to be placed within the subject's vena cava upstream of the junctions of the vena cava with all of the subject's renal veins, and to partially occlude the vena cava, e.g., as described herein with reference to Fig. 22C .
  • upstream and downstream blood pumps are disposed on a single catheter, e.g., as described hereinabove with reference to Figs. 1A-C .
  • an upstream occlusion element, and a downstream blood pump are disposed on a single catheter, e.g., as described herein with reference to Figs. 5A-B , 16 , and 22C .
  • the catheter is introduced into the vena cava from a vein that is above the inferior vena cava (e.g., the jugular vein or the subclavian vein), in which case the upstream pump or occlusion element is disposed upon the catheter distally with respect to the downstream blood pump, as described herein with reference to Figs. 1A and 3 .
  • a vein that is above the inferior vena cava e.g., the jugular vein or the subclavian vein
  • the upstream pump or occlusion element is disposed upon the catheter distally with respect to the downstream blood pump, as described herein with reference to Figs. 1A and 3 .
  • the catheter is introduced into the vena cava from a vein that is below the junctions of the vena cava with the subject's renal veins (e.g., the femoral vein), in which case the upstream pump or occlusion element is disposed upon the catheter proximally with respect to the downstream blood pump, e.g., as described herein with reference to Fig. 4 .
  • Figs. 22A and 22B are schematic illustrations of an occlusion element 290 disposed upon a catheter 291 ( Fig. 22A ), and a blood pump 300 disposed upon a catheter 301 ( Fig. 22B ), the occlusion element or the blood pump being placed in a subject's infra-renal vena cava (i.e., within the vena cava, upstream of junctions of the vena cava with all of a subject's renal veins), in accordance with respective applications of the present invention.
  • occlusion element 290, or blood pump 300 is inserted into the vena cava of a subject suffering from acute heart failure.
  • occlusion element is as described hereinabove with reference to Figs. 5A and 5B , except for differences described hereinbelow.
  • blood pump 300 is generally similar to blood pumps described hereinabove.
  • blood pump 300 may be generally configured like blood pump 24 described hereinabove with reference to Figs. 19A-D .
  • occlusion element 290 is configured to cause partial occlusion of the infra-renal vena cava, or blood pump 300 is used to pump blood in a retrograde direction within the infra-renal vena cava.
  • occlusion element 290 or blood pump 300 in this manner reduces cardiac preload, by causing lower body venous pooling. Typically, reducing cardiac preload ameliorates pulmonary congestion and/or improve cardiac loading conditions and function.
  • a blood pump that is generally similar to that described with reference to Figs. 19A-D is used for the application shown in Fig. 22B . However, it is noted that for applications as shown in Fig. 22B , blood pump 300 typically does not include material 262 (shown in Fig. 19A , for example) since it is desirable to allow antegrade blood flow through the vena cava around the outside of the region that immediately surrounds the impeller.
  • infra-renal vena-caval occlusion by occlusion element 290, or infra-renal vena-caval retrograde blood pumping by blood pump 300 on renal and pulmonary function may be highly dependent on patient position. For example, bringing the patient into an upright position, is known to alleviate pulmonary congestion, but to aggravate renal congestion. Moreover, it is important to balance the positive of effects of reducing venous blood pressure against the possible negative effect of causing too great a reduction in cardiac output. This is of particular concern in the severely ill and fragile patient group of acute heart failure, for whom it is critical to avoid a drop in cardiac output.
  • the extent to which occlusion element 290 occludes the infra-renal vena cava, and/or the rate at which blood pump 300 pumps blood is controlled by a control unit 310.
  • occlusion element 290 may include a balloon (as shown), and inflation of the balloon may be controllable.
  • the occlusion element includes a frame (e.g., as shown in Fig. 5B ), which is expandable (e.g., by heating the frame, or by applying an electrical current to the frame).
  • the occlusion element includes a nozzle, the diameter of an opening of which is controllable, e.g., as described in co-pending PCT Patent Application No. PCT/IL2017/051092 to Tuval, filed Sep. 28, 2017 , which is incorporated herein by reference.
  • the extent to which the occlusion element occludes the vena cava is controlled by control unit 310 responsively to the parameters detected by sensors.
  • a first sensor 292 may be disposed upstream of the occlusion element, and a second sensor 294 may be disposed downstream of the occlusion element.
  • the first and second sensors are blood pressure sensors configured to measure, respectively, lower body venous blood pressure and central venous blood pressure.
  • the first and second sensors may be flow sensors, blood velocity sensors, oxygen-saturation sensors, temperature sensors, and/or thermal flow sensors (e.g., as described with reference to Figs. 22Ai-C ii of US 2016/0022890 to Schwammenthal , which is incorporated herein by reference), the first and second sensors being configured to measure lower body venous parameters and central venous parameters, respectively.
  • upstream sensor 292 is mounted upon catheter 291 or catheter 301 at a location that is at least 1.5 cm (e.g., at least 2.5 cm) upstream of occlusion element 290, or upstream of blood pump 300, such that by the time that the blood flow reaches the occlusion element or the blood pump, any effect on the direction of the blood flow caused by the sensor has substantially dissipated.
  • downstream sensor 294 is mounted upon catheter 291 or catheter 301 at a location that is at least 1.5 (e.g., at least 2.5 mm) downstream of occlusion element 290, or downstream of blood pump 300, such that by the time that the blood flow reaches sensor 294, flow layers generated by having passed the occlusion element or the blood pump are sufficiently reunited to permit accurate measurement of flow, pressure, velocity, and/or other parameters as described hereinabove.
  • downstream sensor 294 is mounted upon catheter 291 or catheter 301 at a location that is at least 1.5 (e.g., at least 2.5 mm) downstream of the junction of the vena cava with the right renal vein, and/or at least 1.5 (e.g., at least 2.5 mm) downstream of junctions of the vena cava with the all of the subject's renal veins.
  • Fig. 23 is a curve showing the relationship between (a) cardiac preload and (b) cardiac output and/or arterial pressure, when the occlusion element of Fig. 22A or the blood pump of Fig. 22B is used, in accordance with some applications of the present invention.
  • an indication of cardiac preload is measured, for example, by measuring central venous pressure (e.g., using sensor 294), renal venous pressure, cardiac diameter and/or cardiac volume.
  • an indication of cardiac output and/or arterial pressure is measured, for example, by measuring arterial blood flow, minute flow, arterial flow velocity, and/or arterial blood pressure.
  • control unit 310 monitors the indication of cardiac preload, and modulates the extent to which the occlusion element occludes the infra-renal vena cava, and/or the rate at which the blood pump pumps blood, in response thereto.
  • control unit is configured to modulates the extent to which the occlusion element occludes the infra-renal vena cava, and/or the rate at which the blood pump pumps blood, by first (algorithmically) generating a pressure-flow curve, e.g., as shown in Fig. 23 .
  • control unit then automatically sets the extent to which the occlusion element occludes the infra-renal vena cava, and/or the rate at which the blood pump pumps blood, by determining the highest degree of obstruction, or reverse blood flow, attainable without decreasing cardiac output and/or arterial pressure by more than a given threshold.
  • central venous blood pressure and blood flow may be at position 1 upon the curve shown in Fig. 23 .
  • the cardiac preload and cardiac output and/or arterial pressure moves along the curve from position 2, through to position 6.
  • point 4 may be the optimal level of cardiac preload reduction, since there is a substantial reduction in cardiac preload without decreasing cardiac output and/or arterial pressure.
  • the level of reduction in cardiac output and/or arterial pressure may be dangerous for the patient.
  • thermodilution catheter e.g., a commercially available thermodilution catheter
  • a different type of sensor is used to measure cardiac output, in accordance with techniques that are known in the art.
  • Control unit 310 is configured to receive the measured cardiac output and to use the measured cardiac output as an input signal for determining the extent to which the occlusion element should occlude the infra-renal vena cava, and/or the rate at which the blood pump should pump blood, in accordance with the techniques described hereinabove.
  • arterial blood pressure may be measured and may be used as an input signal for the control unit to determine the extent to which the occlusion element should occlude the infra-renal vena cava, and/or the rate at which the blood pump should pump blood.
  • the control unit may be configured to detect a relationship between decreases in central venous pressure and corresponding decreases in arterial pressure. The control unit may then be configured to set the level of occlusion or the rate of pumping, such that there is no decrease in arterial pressure, or such that the decrease in arterial pressure is below a given threshold, in accordance with the techniques described hereinabove.
  • Fig. 22C is a schematic illustration of a catheter 314 is placed into a subject's vena cava, the catheter including a downstream pump 320 and an occlusion element, such as balloon 290, in accordance with some applications of the present invention.
  • the downstream pump is generally similar to pump 24 described with reference to Figs. 19A-D .
  • a different one of the pumps described hereinabove is used.
  • the occlusion element is similar to any of the occlusion elements described hereinabove.
  • the extent to which the occlusion element occludes the vena cava can be controlled, e.g., using techniques as described hereinabove.
  • the downstream pump is placed downstream of the junctions of the vena cava with all of the subject's renal veins, and pumps blood through the vena cava, in the downstream direction, away from the junctions of the vena cava with the renal veins.
  • the occlusion element is placed upstream of the junctions of the vena cava with all of the subject's renal veins and is configured to partially occlude the subject's vena cava upstream of the junctions of the vena cava with the subject's renal veins.
  • the occlusion element is configured to partially occlude the subject's vena cava such that, in response to the pumping of the downstream blood pump, there is not a substantial increase of blood flow from the subject's lower body toward the subject heart, but such that a region of low pressure within the vena cava is generated, between the occlusion element and the downstream blood pump, within which the blood pressure is lower than the subject's central venous pressure.
  • a region of low pressure blood flow from the renal veins into the vena cava increases, thereby lowering renal blood pressure and enhancing renal perfusion.
  • the combination of the downstream pump and the upstream occlusion element is configured such that the overall effect of the downstream pump and the upstream occlusion element is that (a) central venous pressure is lowered relative to lower body venous pressure (e.g., by the pumping of the downstream pump not fully compensating for the reduction in pressure caused by the occlusion of the vena cava by the upstream occlusion element), and (b) renal venous pressure is lowered relative to lower body venous pressure and central venous pressure, due to the region of low pressure being generated within the vena cava, between the occlusion element and the downstream blood pump.
  • the overall effect of the downstream pump and the upstream occlusion element is that (a) central venous pressure is lowered relative to lower body venous pressure (e.g., by the pumping of the downstream pump not fully compensating for the reduction in pressure caused by the occlusion of the vena cava by the upstream occlusion element), and (b) renal venous
  • sensor 292 is disposed upstream of the occlusion element and is configured to measure a parameter that is indicative of lower body venous pressure
  • sensor 294 is disposed downstream of the blood pump and is configured to measure a parameter that is indicative of central venous pressure
  • sensor 296 is disposed between the occlusion element and the blood pump, and is configured to measure a parameter that is indicative of renal venous pressure.
  • sensors 292, 294, and/or 296 may be pressure sensors, flow sensors, blood velocity sensors, oxygen-saturation sensors, temperature sensors, and/or thermal flow sensors.
  • control unit 310 controls the extent to which the occlusion element occludes the vena cava and the rate at which the pump pumps blood, responsively to one or more of the parameters detected by the sensors. For example, based upon the parameters detected by the sensors, the control unit may control the extent to which the occlusion element occludes the vena cava and the rate at which the pump pumps blood in coordination with each other, such that the ratio between renal venous pressure and lower body pressure is a first ratio, and such that the ratio between central venous pressure and lower body pressure is a second ratio, which is different from the first ratio.
  • the first ratio is designated based upon the extent to which it is desirable to decrease the subject's renal venous pressure, such as to increase renal perfusion, in accordance with the techniques described herein.
  • the second ratio is designated based upon the extent to which it is desirable to decrease the subject's cardiac preload, in accordance with the techniques described herein.
  • control unit 310 typically includes a computer processor that comprises circuitry and that is configured to execute the actions described herein.
  • the operations described herein that are performed by the computer processor transform the physical state of a memory, which is a real physical article that is in communication with the computer processor, to have a different magnetic polarity, electrical charge, or the like, depending on the technology of the memory that is used.
  • Control unit 310 is typically a hardware device programmed with computer program instructions to produce a special-purpose computer. For example, when programmed to perform the techniques described herein, control unit 310 typically acts as a special-purpose, preload-modulating computer processor. For some applications, a user interacts with the computer processor via a user interface 312, which is typically generally similar to user interface 54 described hereinabove.
  • the scope of the present invention includes using any other type of pump for pumping blood in the manner described herein, mutatis mutandis.
  • a roller pump an Archimedes screw pump, a centrifugal pump, a pneumatic pump, and/or a compression pump may be used.

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Families Citing this family (48)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9597205B2 (en) 2012-06-06 2017-03-21 Magenta Medical Ltd. Prosthetic renal valve
US10857274B2 (en) 2012-11-06 2020-12-08 Queen Mary University Of London Mechanical circulatory support device with centrifugal impeller designed for implantation in the descending aorta
CA2905349C (fr) 2013-03-13 2021-10-19 Magenta Medical Ltd. Pompe renale
US10583231B2 (en) 2013-03-13 2020-03-10 Magenta Medical Ltd. Blood pump
US11291824B2 (en) 2015-05-18 2022-04-05 Magenta Medical Ltd. Blood pump
US11524153B2 (en) 2016-10-03 2022-12-13 Queen Mary University Of London Mechanical circulatory support device with axial flow turbomachine optimized for heart failure and cardio-renal syndrome by implantation in the descending aorta
EP3532120B1 (fr) 2016-10-25 2024-05-01 Magenta Medical Ltd. Dispositif d'assistance ventriculaire
EP3544649B1 (fr) 2016-11-23 2023-06-07 Magenta Medical Ltd. Pompes à sang
EP4233989A3 (fr) * 2017-06-07 2023-10-11 Shifamed Holdings, LLC Dispositifs de déplacement de fluide intravasculaire, systèmes et procédés d'utilisation
US10595874B2 (en) 2017-09-21 2020-03-24 W. L. Gore & Associates, Inc. Multiple inflation endovascular medical device
EP3710076B1 (fr) 2017-11-13 2023-12-27 Shifamed Holdings, LLC Dispositifs de déplacement de liquide intravasculaire, systèmes et procédés d'utilisation
WO2019138350A2 (fr) 2018-01-10 2019-07-18 Magenta Medical Ltd Dispositif d'assistance ventriculaire
US10905808B2 (en) 2018-01-10 2021-02-02 Magenta Medical Ltd. Drive cable for use with a blood pump
DE102018201030A1 (de) 2018-01-24 2019-07-25 Kardion Gmbh Magnetkuppelelement mit magnetischer Lagerungsfunktion
EP4085965A1 (fr) 2018-02-01 2022-11-09 Shifamed Holdings, LLC Pompes à sang intravasculaires et procédés d'utilisation et de fabrication
WO2019195480A1 (fr) * 2018-04-04 2019-10-10 Theodosios Korakianitis Dispositif mécanique amovible d'assistance circulatoire destiné à être utilisé à court terme
US11690997B2 (en) 2018-04-06 2023-07-04 Puzzle Medical Devices Inc. Mammalian body conduit intralumenal device and lumen wall anchor assembly, components thereof and methods of implantation and explanation thereof
DE102018211327A1 (de) 2018-07-10 2020-01-16 Kardion Gmbh Laufrad für ein implantierbares, vaskuläres Unterstützungssystem
US11202900B2 (en) * 2018-07-31 2021-12-21 Cardiovascular Systems, Inc. Intravascular pump with controls and display screen on handle
US20200246527A1 (en) 2018-10-05 2020-08-06 Daniel Hildebrand Intravascular blood pumps and methods of use
US11484698B2 (en) * 2019-07-09 2022-11-01 Boston Scientific Scimed, Inc. Circulatory support device
EP3749383B1 (fr) 2019-01-24 2021-04-28 Magenta Medical Ltd. Dispositif d'assistance ventriculaire
US20200288988A1 (en) * 2019-03-14 2020-09-17 Abiomed, Inc. Blood Flow Rate Measurement System
JP7441856B2 (ja) * 2019-04-17 2024-03-01 ダブリュ．エル．ゴア アンド アソシエイツ，インコーポレイティド 心不全患者の体液過剰の急性治療のための方法及びデバイス
AU2020277752A1 (en) 2019-05-23 2021-11-25 Magenta Medical Ltd Blood pumps
WO2020247612A1 (fr) * 2019-06-05 2020-12-10 Shifamed Holdings, Llc Pompes d'assistance circulatoire de cathéter et procédés d'utilisation et de fabrication
EP3990095A4 (fr) 2019-06-28 2023-07-12 Theodosios Alexander Support circulatoire mécanique amovible pour utilisation à court terme
WO2021011473A1 (fr) 2019-07-12 2021-01-21 Shifamed Holdings, Llc Pompes à sang intravasculaires et méthode d'utilisation et procédé de fabrication
WO2021016372A1 (fr) 2019-07-22 2021-01-28 Shifamed Holdings, Llc Pompes à sang intravasculaires à entretoises et procédés d'utilisation et de fabrication
WO2021062265A1 (fr) 2019-09-25 2021-04-01 Shifamed Holdings, Llc Dispositifs et systèmes de pompes à sang intravasculaires et leurs procédés d'utilisation et de commande
CN115279448A (zh) 2019-12-03 2022-11-01 普罗西里翁公司 血泵
EP4072649A4 (fr) * 2019-12-13 2024-02-14 Procyrion Inc Structures de support pour pompes à sang intravasculaires
DE102020102474A1 (de) 2020-01-31 2021-08-05 Kardion Gmbh Pumpe zum Fördern eines Fluids und Verfahren zum Herstellen einer Pumpe
US20230137473A1 (en) 2020-04-02 2023-05-04 Magenta Medical Ltd Centrifugal and mixed-flow impellers for use with a blood pump
EP3956010B1 (fr) 2020-04-07 2023-02-08 Magenta Medical Ltd. Dispositif d'assistance ventriculaire
CN111568426B (zh) * 2020-05-25 2023-03-24 易荔 气道狭窄段直径和长度测量装置
EP3915607A1 (fr) * 2020-05-26 2021-12-01 Systol Dynamics Dispositif de déchargement du ventricule gauche
US20210378677A1 (en) * 2020-06-08 2021-12-09 White Swell Medical Ltd Non-thrombogenic devices for treating edema
EP4149606B1 (fr) 2021-03-09 2023-10-04 Magenta Medical Ltd. Dispositif d'assistance ventriculaire
EP4271461B1 (fr) 2021-10-11 2024-03-13 Magenta Medical Ltd. Dispositif d'assistance ventriculaire
WO2023091379A1 (fr) * 2021-11-16 2023-05-25 Theodosios Alexander Dispositif de support circulatoire mécanique repliable à usage temporaire
WO2023107833A1 (fr) * 2021-12-08 2023-06-15 Fbr Medical, Inc. Pompe d'assistance circulatoire à cathéter avec attache anti-migration intra-cardiaque déployable
WO2023148555A2 (fr) * 2022-02-03 2023-08-10 White Swell Medical Ltd Console et système de gestion de fluide
TW202406505A (zh) * 2022-03-18 2024-02-16 美商阿比奥梅德公司 血液泵血液相容性裝置
WO2023212361A1 (fr) 2022-04-29 2023-11-02 inQB8 Medical Technologies, LLC Systèmes, dispositifs et procédés pour occlure, restreindre et dévier de manière sélective et commandée un flux dans le système vasculaire de patient
US11883030B2 (en) 2022-04-29 2024-01-30 inQB8 Medical Technologies, LLC Systems, devices, and methods for controllably and selectively occluding, restricting, and diverting flow within a patient's vasculature
WO2024057257A2 (fr) 2022-09-14 2024-03-21 Magenta Medical Ltd Partie tête de pompe d'un dispositif d'assistance ventriculaire
CN116271501A (zh) * 2023-04-26 2023-06-23 苏州心擎医疗技术有限公司 导管泵

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2013183060A2 (fr) 2012-06-06 2013-12-12 Magenta Medical Ltd. Valve rénale prothétique
WO2014141284A2 (fr) 2013-03-13 2014-09-18 Magenta Medical Ltd. Pompe rénale
US20150157777A1 (en) 2013-12-11 2015-06-11 Magenta Medical Ltd Curved catheter
WO2015177793A2 (fr) 2014-05-19 2015-11-26 Magenta Medical Ltd. Pompe à sang
WO2016185473A1 (fr) 2015-05-18 2016-11-24 Magenta Medical Ltd. Pompe à sang
US20170100527A1 (en) 2013-03-13 2017-04-13 Magenta Medical Ltd. Blood pump

Family Cites Families (226)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE1033690B (de) 1955-04-26 1958-07-10 Caterpillar Tractor Co Verfahren und Vorrichtung zum Abschrecken eines erhitzten Stahlwerkstueckes beliebigen Querschnitts mittels eines stroemenden Abschreckmittels
US4822345A (en) 1986-08-14 1989-04-18 Danforth John W Controllable flexibility catheter
US4886506A (en) 1986-12-23 1989-12-12 Baxter Travenol Laboratories, Inc. Soft tip catheter
US5066282A (en) 1987-09-23 1991-11-19 Leocor, Inc. Positive displacement piston driven blood pump
US4919647A (en) 1988-10-13 1990-04-24 Kensey Nash Corporation Aortically located blood pumping catheter and method of use
US4954055A (en) 1989-06-22 1990-09-04 Baxter International, Inc. Variable roller pump tubing
US5300112A (en) 1992-07-14 1994-04-05 Aai Corporation Articulated heart pump
SE501215C2 (sv) 1992-09-02 1994-12-12 Oeyvind Reitan Kateterpump
US5713730A (en) 1992-09-04 1998-02-03 Kyocera Corporation Ceramic pivot bearing arrangement for a sealless blood pump
US5957672A (en) 1993-11-10 1999-09-28 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Blood pump bearing system
US5613935A (en) 1994-12-16 1997-03-25 Jarvik; Robert High reliability cardiac assist system
US5772693A (en) 1996-02-09 1998-06-30 Cardiac Control Systems, Inc. Single preformed catheter configuration for a dual-chamber pacemaker system
DE19613564C1 (de) 1996-04-04 1998-01-08 Guenter Prof Dr Rau Intravasale Blutpumpe
IL118352A0 (en) 1996-05-21 1996-09-12 Sudai Amnon Apparatus and methods for revascularization
JP3563540B2 (ja) 1996-09-13 2004-09-08 テルモ株式会社 カテーテル
US5964694A (en) 1997-04-02 1999-10-12 Guidant Corporation Method and apparatus for cardiac blood flow assistance
JP2002512821A (ja) 1998-01-12 2002-05-08 クライン，エンリケ ジェイ． 改良シールレス血液ポンプ
JPH11244376A (ja) 1998-02-27 1999-09-14 Kyocera Corp 血液ポンプ
DE29804046U1 (de) 1998-03-07 1998-04-30 Schmitz Rode Thomas Dipl Ing D Perkutan implantierbare selbstentfaltbare Axialpumpe zur temporären Herzunterstützung
US6086527A (en) 1998-04-02 2000-07-11 Scimed Life Systems, Inc. System for treating congestive heart failure
US6749598B1 (en) 1999-01-11 2004-06-15 Flowmedica, Inc. Apparatus and methods for treating congestive heart disease
US7780628B1 (en) 1999-01-11 2010-08-24 Angiodynamics, Inc. Apparatus and methods for treating congestive heart disease
US20050165269A9 (en) 1999-06-18 2005-07-28 Aboul-Hosn Walid N. Cannulation system and related methods
US6247892B1 (en) 1999-07-26 2001-06-19 Impsa International Inc. Continuous flow rotary pump
WO2001007787A1 (fr) 1999-07-26 2001-02-01 Impsa International Inc. Pompe rotative a courant continu
US6136025A (en) 1999-07-27 2000-10-24 Barbut; Denise R. Endoscopic arterial pumps for treatment of cardiac insufficiency and venous pumps for right-sided cardiac support
US8257428B2 (en) * 1999-08-09 2012-09-04 Cardiokinetix, Inc. System for improving cardiac function
US7655016B2 (en) * 1999-09-17 2010-02-02 Covidien Mechanical pump for removal of fragmented matter and methods of manufacture and use
US6585758B1 (en) 1999-11-16 2003-07-01 Scimed Life Systems, Inc. Multi-section filamentary endoluminal stent
DE29921352U1 (de) 1999-12-04 2001-04-12 Impella Cardiotech Ag Intravasale Blutpumpe
US6592567B1 (en) 1999-12-07 2003-07-15 Chf Solutions, Inc. Kidney perfusion catheter
US6551344B2 (en) * 2000-04-26 2003-04-22 Ev3 Inc. Septal defect occluder
DE10040403A1 (de) 2000-08-18 2002-02-28 Impella Cardiotech Ag Intrakardiale Blutpumpe
US6616624B1 (en) 2000-10-30 2003-09-09 Cvrx, Inc. Systems and method for controlling renovascular perfusion
AU2002229026A1 (en) 2000-11-13 2002-05-21 Young Cho Device and method for reducing blood pressure
US6482228B1 (en) 2000-11-14 2002-11-19 Troy R. Norred Percutaneous aortic valve replacement
DE10060275A1 (de) 2000-12-05 2002-06-13 Impella Cardiotech Ag Verfahren zum Kalibrieren eines Drucksensors oder eines Flussensors an einer Rotationspumpe
US8038708B2 (en) 2001-02-05 2011-10-18 Cook Medical Technologies Llc Implantable device with remodelable material and covering material
US20020107536A1 (en) 2001-02-07 2002-08-08 Hussein Hany M. Device and method for preventing kidney failure
AU2002250250A1 (en) 2001-03-01 2002-09-19 Three Arch Partners Intravascular device for treatment of hypertension
US8091556B2 (en) 2001-04-20 2012-01-10 V-Wave Ltd. Methods and apparatus for reducing localized circulatory system pressure
US20040210236A1 (en) 2001-07-09 2004-10-21 Mats Allers Flow path control catheter with funnel-shaped expandable structure at proximal part and tubular-shaped structure at distal part and perfusion system with such a catheter
US20030055486A1 (en) 2001-09-19 2003-03-20 Adams John M. Vascular reinforcement device and method
CA2981561C (fr) 2001-10-04 2020-08-25 Neovasc Medical Ltd. Implant reducteur de flux
WO2003068306A1 (fr) 2001-10-30 2003-08-21 Applied Medical Resources Corporation Catheter d'exclusion vasculaire
AU2003236497A1 (en) 2002-06-11 2003-12-22 Walid Aboul-Hosn Expandable blood pump and related methods
US6884210B2 (en) 2002-06-12 2005-04-26 Miwatec Incorporated Blood pump
WO2004014474A1 (fr) 2002-08-08 2004-02-19 Neovasc Medical Ltd. Implant reducteur de flux
AU2003276903A1 (en) 2002-09-20 2004-05-04 Flowmedica, Inc. Method and apparatus for selective material delivery via an intra-renal catheter
EP1585572A4 (fr) 2002-09-20 2010-02-24 Flowmedica Inc Procede et appareil pour administrer une substance intra-aortique a un vaisseau ramifie
US20050197624A1 (en) 2004-03-04 2005-09-08 Flowmedica, Inc. Sheath for use in peripheral interventions
AU2003293373A1 (en) 2002-12-06 2004-06-30 World Heart Corporation Miniature, pulsatile implantable ventricular assist devices and methods of controlling ventricular assist devices
US20040111006A1 (en) 2002-12-17 2004-06-10 Scout Medical Technologies, Llc System and method for regulating blood pressure
IL154531A (en) 2003-02-19 2006-04-10 Yair Tal Method and system for regulating blood flow
US20040163655A1 (en) 2003-02-24 2004-08-26 Plc Systems Inc. Method and catheter system applicable to acute renal failure
EP1596903A2 (fr) 2003-02-25 2005-11-23 The Cleveland Clinic Foundation Appareil et procede d'auto-retroperfusion d'une veine coronaire
US7159593B2 (en) 2003-04-17 2007-01-09 3F Therapeutics, Inc. Methods for reduction of pressure effects of cardiac tricuspid valve regurgitation
US7717952B2 (en) 2003-04-24 2010-05-18 Cook Incorporated Artificial prostheses with preferred geometries
WO2004096100A1 (fr) 2003-04-24 2004-11-11 Cook Incorporated Prothese a valve artificielle, a dynamique d'ecoulement amelioree
JP2006526464A (ja) 2003-06-05 2006-11-24 フローメディカ，インコーポレイテッド 分枝した身体管腔において両側介入または診断を行うためのシステムおよび方法
US7201772B2 (en) 2003-07-08 2007-04-10 Ventor Technologies, Ltd. Fluid flow prosthetic device
US20050033406A1 (en) 2003-07-15 2005-02-10 Barnhart William H. Branch vessel stent and graft
DE10336902C5 (de) 2003-08-08 2019-04-25 Abiomed Europe Gmbh Intrakardiale Pumpvorrichtung
WO2005020848A2 (fr) 2003-08-28 2005-03-10 Advanced Research And Technology Institute, Inc. Dispositif d'assistance cavopulmonaire et procede associe
US20050049692A1 (en) 2003-09-02 2005-03-03 Numamoto Michael J. Medical device for reduction of pressure effects of cardiac tricuspid valve regurgitation
US6984411B2 (en) 2003-10-14 2006-01-10 Boston Scientific Scimed, Inc. Method for roll coating multiple stents
US7763011B2 (en) 2003-12-22 2010-07-27 Boston Scientific Scimed, Inc. Variable density braid stent
WO2005074384A2 (fr) 2004-02-10 2005-08-18 Yossi Gross Dispositif d'amplification d'ecoulement sanguin extracardiaque
WO2006026805A1 (fr) 2004-09-07 2006-03-16 Droneon Pty Limited Dispositifs et systemes d'acces peripherique
US7393181B2 (en) 2004-09-17 2008-07-01 The Penn State Research Foundation Expandable impeller pump
US20060064059A1 (en) 2004-09-21 2006-03-23 Mark Gelfand Treatment of infarct expansion by partially occluding vena cava
DE102004054714A1 (de) 2004-11-12 2006-05-24 Impella Cardiosystems Gmbh Faltbare intravasal einführbare Blutpumpe
US7744642B2 (en) 2004-11-19 2010-06-29 Biomedical Research Associates, Inc. Prosthetic venous valves
US8419609B2 (en) 2005-10-05 2013-04-16 Heartware Inc. Impeller for a rotary ventricular assist device
US7972122B2 (en) 2005-04-29 2011-07-05 Heartware, Inc. Multiple rotor, wide blade, axial flow pump
US7402151B2 (en) 2004-12-17 2008-07-22 Biocardia, Inc. Steerable guide catheters and methods for their use
DE102005017546A1 (de) 2005-04-16 2006-10-19 Impella Cardiosystems Gmbh Verfahren zur Steuerung einer Blutpumpe
US7569071B2 (en) 2005-09-21 2009-08-04 Boston Scientific Scimed, Inc. Venous valve, system, and method with sinus pocket
AU2013257469B2 (en) 2005-10-05 2016-03-17 Heartware, Inc. Axial flow pump with multi-grooved rotor
AU2013205145B2 (en) 2005-10-05 2013-08-15 Heartware, Inc. Axial flow pump with multi-grooved rotor
US7758531B2 (en) 2006-03-02 2010-07-20 Vinod Patel Method and apparatus for treatment of congestive heart disease
EP3800357B1 (fr) 2006-03-23 2024-05-08 The Penn State Research Foundation Dispositif d'assistance cardiaque à pompe à turbine extensible
US9162019B2 (en) 2006-04-26 2015-10-20 The Cleveland Clinic Foundation Two-stage rotodynamic blood pump
US20070293808A1 (en) 2006-04-27 2007-12-20 Williams Michael S Renal blood flow augmentation for congestive heart failure treatment
US20080004485A1 (en) 2006-06-30 2008-01-03 Moreschi Rafael M Trans-Septal Heart Assist Devices and Methods of Use
US7717844B2 (en) 2006-07-06 2010-05-18 Apaxis Medical, Inc. Method and apparatus for stabilization and positioning during surgery
US10624621B2 (en) 2006-11-07 2020-04-21 Corvia Medical, Inc. Devices and methods for the treatment of heart failure
US20080132748A1 (en) 2006-12-01 2008-06-05 Medical Value Partners, Llc Method for Deployment of a Medical Device
US8303649B2 (en) 2007-01-29 2012-11-06 Cook Medical Technologies Llc Artificial venous valve with discrete shaping members
WO2008094706A2 (fr) 2007-02-01 2008-08-07 Cook Incorporated Dispositif de fermeture et procédé de fermeture d'une ouverture corporelle
WO2008128070A2 (fr) 2007-04-11 2008-10-23 The Cleveland Clinic Foundation Appareil et procédé de neuromodulation rénale
US7762941B2 (en) 2007-04-25 2010-07-27 Robert Jarvik Blood pump bearings with separated contact surfaces
CA2693227A1 (fr) 2007-07-13 2009-01-22 Yigal Gat Methodes et appareil pour le traitement de la prostate
US8079948B2 (en) 2007-08-29 2011-12-20 NuCardia, Inc. Article comprising an impeller
ATE480274T1 (de) 2007-10-08 2010-09-15 Ais Gmbh Aachen Innovative Sol Katheter-vorrichtung
ATE491483T1 (de) 2007-10-08 2011-01-15 Ais Gmbh Aachen Innovative Solutions Katheter-vorrichtung
US8489190B2 (en) 2007-10-08 2013-07-16 Ais Gmbh Aachen Innovative Solutions Catheter device
US8439859B2 (en) 2007-10-08 2013-05-14 Ais Gmbh Aachen Innovative Solutions Catheter device
US20090131785A1 (en) 2007-11-15 2009-05-21 University Of Florida Research Foundation, Inc. Variable occlusional balloon catheter assembly
WO2009091968A1 (fr) 2008-01-18 2009-07-23 Med Institute, Inc. Système de fixation de dispositif intravasculaire muni de supports
EP2254514B1 (fr) 2008-01-24 2018-10-03 Medtronic, Inc Stents pour des valvules cardiaques prothétiques
EP2695587A1 (fr) 2008-01-25 2014-02-12 JenaValve Technology Inc. Appareil médical pour le traitement thérapeutique d'une valvule cardiaque insuffisante
US8538535B2 (en) 2010-08-05 2013-09-17 Rainbow Medical Ltd. Enhancing perfusion by contraction
EP2293745A1 (fr) 2008-04-18 2011-03-16 Cook Incorporated Prothèse de vaisseau ramifié
US10245165B2 (en) 2009-04-02 2019-04-02 Q3 Medical Devices Limited Stent
ES2449221T3 (es) 2008-06-23 2014-03-18 Cardiobridge Gmbh Bomba de catéter para apoyo circulatorio
EP2346405B1 (fr) 2008-09-26 2019-03-13 Vascular Dynamics Inc. Dispositifs et procédés de contrôle de la tension artérielle
AU2009302471B2 (en) 2008-10-06 2015-03-19 Indiana University Research And Technology Corporation Methods and apparatus for active or passive assistance in the circulatory system
AT507578B1 (de) 2008-11-27 2011-06-15 Miracor Medical Systems Gmbh Implantierbare vorrichtung zur intermittierenden okklusion eines blutgefässes
EP2194278A1 (fr) 2008-12-05 2010-06-09 ECP Entwicklungsgesellschaft mbH Pompe à fluide dotée d'un rotor
US8923970B2 (en) 2008-12-09 2014-12-30 Nephera Ltd. Stimulation of the urinary system
EP2218469B1 (fr) 2009-02-12 2012-10-31 ECP Entwicklungsgesellschaft mbH Boîtier pour un élément fonctionnel
EP2229965A1 (fr) 2009-03-18 2010-09-22 ECP Entwicklungsgesellschaft mbH Pompe à fluide dotée d'une forme spéciale de lame de rotor
EP2246078A1 (fr) 2009-04-29 2010-11-03 ECP Entwicklungsgesellschaft mbH Agencement d'arbres doté d'un arbre se déroulant à l'intérieur d'une enveloppe rempli de fluide
EP2248544A1 (fr) 2009-05-05 2010-11-10 ECP Entwicklungsgesellschaft mbH Pompe à fluide à diamètre modifiable, notamment à des fins médicales
US8858613B2 (en) 2010-09-20 2014-10-14 Altura Medical, Inc. Stent graft delivery systems and associated methods
EP2432515B1 (fr) 2009-05-18 2014-05-07 Cardiobridge GmbH Pompe de cathéter
WO2010150208A2 (fr) 2009-06-23 2010-12-29 Endospan Ltd. Prothèses vasculaires utilisées pour le traitement des anévrismes
EP2266640A1 (fr) 2009-06-25 2010-12-29 ECP Entwicklungsgesellschaft mbH Pale comprimable et extensible pour une pompe à fluide
JP5815516B2 (ja) 2009-07-01 2015-11-17 ザ・ペン・ステイト・リサーチ・ファウンデイションＴｈｅ Ｐｅｎｎ Ｓｔａｔｅ Ｒｅｓｅａｒｃｈ Ｆｏｕｎｄａｔｉｏｎ 拡張可能なカニューレを備える血液ポンプ
EP2282070B1 (fr) 2009-08-06 2012-10-17 ECP Entwicklungsgesellschaft mbH Dispositif de cathéter doté d'un dispositif d'accouplement pour un dispositif d'entraînement
EP2475415B1 (fr) 2009-09-09 2016-06-22 Abiomed, Inc. Procédé pour envoyer simultanément un fluide vers un cathéter à double lumière à partir d'une source de fluide unique
DK3441616T3 (da) 2009-09-22 2023-05-30 Ecp Entw Mbh Komprimerbar rotor til en fluidpumpe
EP2298373A1 (fr) 2009-09-22 2011-03-23 ECP Entwicklungsgesellschaft mbH Pompe à fluide dotée d'au moins une aube directrice et d'un dispositif d'appui
EP2298372A1 (fr) 2009-09-22 2011-03-23 ECP Entwicklungsgesellschaft mbH Rotor pour une pompe axiale pour le transport d'un fluide
EP2298371A1 (fr) 2009-09-22 2011-03-23 ECP Entwicklungsgesellschaft mbH Elément fonctionnel, notamment pompe à fluide, doté d'un boîtier et d'un élément de transport
US9174065B2 (en) 2009-10-12 2015-11-03 Kona Medical, Inc. Energetic modulation of nerves
EP2314331B1 (fr) 2009-10-23 2013-12-11 ECP Entwicklungsgesellschaft mbH Agencement de pompes de cathéter et agencement d'arbres flexible doté d'une âme
US8690749B1 (en) * 2009-11-02 2014-04-08 Anthony Nunez Wireless compressible heart pump
JP2013509941A (ja) 2009-11-09 2013-03-21 デルキャス システムズ、インク． 治療剤の局所投与により恒常性を維持しながら臓器疾患を治療するシステムおよび方法
US8734508B2 (en) 2009-12-21 2014-05-27 Boston Scientific Scimed, Inc. Systems and methods for making and using percutaneously-delivered pumping systems for providing hemodynamic support
EP2338540A1 (fr) 2009-12-23 2011-06-29 ECP Entwicklungsgesellschaft mbH Palette de transport pour un rotor pouvant être comprimé
EP2338541A1 (fr) 2009-12-23 2011-06-29 ECP Entwicklungsgesellschaft mbH Rotor radial pouvant être comprimé et extensible pour une pompe à fluide
WO2011094521A2 (fr) 2010-01-29 2011-08-04 Dc Devices, Inc. Dispositifs et procédés de réduction de la pression veineuse
EP2363157A1 (fr) 2010-03-05 2011-09-07 ECP Entwicklungsgesellschaft mbH Dispositif destiné à l'action mécanique sur un milieu, notamment pompe à fluide
EP2566555A1 (fr) 2010-03-06 2013-03-13 Nfusion Vascular Systems, LLC Ensemble cathéter de récupération
US8870863B2 (en) 2010-04-26 2014-10-28 Medtronic Ardian Luxembourg S.A.R.L. Catheter apparatuses, systems, and methods for renal neuromodulation
EP2388029A1 (fr) 2010-05-17 2011-11-23 ECP Entwicklungsgesellschaft mbH Agencement de pompe
WO2012002944A1 (fr) 2010-06-29 2012-01-05 Artventive Medical Group, Inc. Réduction d'un écoulement à travers une structure tubulaire
EP2407187A3 (fr) 2010-07-15 2012-06-20 ECP Entwicklungsgesellschaft mbH Pompe sanguine pour l'application invasive à l'intérieur d'un corps de patient
EP2407185A1 (fr) 2010-07-15 2012-01-18 ECP Entwicklungsgesellschaft mbH Rotor pouvant être comprimé et étendu radialement pour une pompe dotée d'une aube directrice
EP2407186A1 (fr) 2010-07-15 2012-01-18 ECP Entwicklungsgesellschaft mbH Rotor pour une pompe, fabriquée à l'aide d'une matière première élastique
US9561094B2 (en) 2010-07-23 2017-02-07 Nfinium Vascular Technologies, Llc Devices and methods for treating venous diseases
CN107349009B (zh) 2010-08-05 2020-06-26 美敦力Af卢森堡有限责任公司 用于肾神经调制的低温消融装置、系统及方法
MX2013004437A (es) 2010-10-25 2013-07-17 Medtronic Ardian Luxembourg Aparatos de cateter que tienen series de multiples electrodos para la neuromodulacion renal y sistemas y metodos asociados.
ES2786754T3 (es) 2010-12-01 2020-10-13 Abiomed Inc Lumen de guía de carga
US8562509B2 (en) * 2010-12-30 2013-10-22 Cook Medical Technologies Llc Ventricular assist device
US9138518B2 (en) 2011-01-06 2015-09-22 Thoratec Corporation Percutaneous heart pump
US20130053732A1 (en) 2011-08-24 2013-02-28 Richard R. Heuser Devices and methods for treating hypertension with energy
US8734331B2 (en) 2011-08-29 2014-05-27 Minnetronix, Inc. Expandable blood pumps and methods of their deployment and use
US9162017B2 (en) 2011-08-29 2015-10-20 Minnetronix, Inc. Expandable vascular pump
US8849398B2 (en) 2011-08-29 2014-09-30 Minnetronix, Inc. Expandable blood pump for cardiac support
DE102011053988B3 (de) 2011-09-27 2012-11-29 E.S. BIO-Tech Ltd. Ausgleichsgefäß
WO2013084235A2 (fr) 2011-12-04 2013-06-13 Endospan Ltd. Système de greffon de stent ramifié
EP2607712B1 (fr) 2011-12-22 2016-07-13 ECP Entwicklungsgesellschaft mbH Boîtier de pompe doté d'un espace intérieur destiné à la réception d'un rotor de pompe
CN104185481B (zh) 2012-02-07 2017-02-22 赫莱达雅公司 血液动力学辅助设备
DE102012202411B4 (de) 2012-02-16 2018-07-05 Abiomed Europe Gmbh Intravasale blutpumpe
EP2819736A1 (fr) 2012-03-01 2015-01-07 Medical Device Works NV Dispositif de perfusion-occlusion
EP2830675A4 (fr) 2012-03-26 2016-01-27 Procyrion Inc Systèmes et procédés de circulation et de perfusion permettant d'améliorer l'écoulement et/ou la pression des liquides organiques
DE102012207056B4 (de) 2012-04-27 2021-11-11 Abiomed Europe Gmbh Kathethersystem und intravasale blutpumpe mit diesem kathetersystem
DE102012207053A1 (de) 2012-04-27 2013-10-31 Abiomed Europe Gmbh Intravasale rotationsblutpumpe
DE102012207049A1 (de) 2012-04-27 2015-08-13 Abiomed Europe Gmbh Intravasale rotationsblutpumpe
EP2662099B1 (fr) 2012-05-09 2014-09-10 Abiomed Europe GmbH Pompe à sang intravasculaire
US8721517B2 (en) 2012-05-14 2014-05-13 Thoratec Corporation Impeller for catheter pump
DE102013008168A1 (de) 2012-05-14 2013-11-14 Thoratec Corporation Laufrad für Katheterpumpe
US9327067B2 (en) 2012-05-14 2016-05-03 Thoratec Corporation Impeller for catheter pump
US9358329B2 (en) 2012-07-03 2016-06-07 Thoratec Corporation Catheter pump
WO2014008431A1 (fr) 2012-07-05 2014-01-09 BiO2 Medical, Inc. Cathéter veineux central avec gaine à lumières multiples pourvu d'un appareil filtrant pour veine cave et son procédé d'utilisation
JP6050045B2 (ja) 2012-07-20 2016-12-21 テルモ株式会社 冠動脈用カテーテル
EP2692369B1 (fr) * 2012-07-31 2015-04-15 Rheinisch-Westfälische Technische Hochschule Aachen Dispositif de pompe sanguine à écoulement axial
US8777832B1 (en) 2013-03-14 2014-07-15 The University Of Kentucky Research Foundation Axial-centrifugal flow catheter pump for cavopulmonary assistance
US9144638B2 (en) 2013-03-14 2015-09-29 Thoratec Corporation Blood pump rotor bearings
US9308302B2 (en) 2013-03-15 2016-04-12 Thoratec Corporation Catheter pump assembly including a stator
EP3010563B1 (fr) * 2013-06-20 2019-12-04 Anagnostopoulos, Constantinos Appareil à ballonnet intra-aortique, dispositifs d'aide et procédés d'amélioration du débit, de la contrepulsion et de l'hémodynamique
US9986935B2 (en) 2013-06-26 2018-06-05 MGC Diagnostics Corporation On-airway pulmonary function tester
EP2860849B1 (fr) 2013-10-11 2016-09-14 ECP Entwicklungsgesellschaft mbH Moteur comprimable, agencement d'implantation et procédé de positionnement du moteur
EP2868331B1 (fr) 2013-11-01 2016-07-13 ECP Entwicklungsgesellschaft mbH Pompe, notamment pompe à sang
EP2868289A1 (fr) 2013-11-01 2015-05-06 ECP Entwicklungsgesellschaft mbH Cathéter flexible doté d'un arbre d'entraînement
CA2947984C (fr) 2014-05-13 2022-11-22 Abiomed, Inc. Composant de boitier de pompe a sang
ES2912878T3 (es) 2014-05-13 2022-05-30 Abiomed Inc Conjunto de cánula
EP3148604B1 (fr) 2014-05-29 2020-09-30 St Vincent's Hospital Sydney Limited Méthode et appareil de dispositif d'assistance ventriculaire
US9901722B2 (en) 2014-06-01 2018-02-27 White Swell Medical Ltd System and method for treatment of pulmonary edema
US10245363B1 (en) 2014-06-17 2019-04-02 Stanton J. Rowe Catheter-based pump for improving organ function
EP3789054A1 (fr) 2014-07-04 2021-03-10 Abiomed Europe GmbH Tube de gaine pour l'accès étanche à un vaisseau
JP7088674B2 (ja) 2015-04-30 2022-06-21 エーツェーペー エントヴィッケルングゲゼルシャフト エムベーハー 流体ポンプ用ロータならびにその作成方法および金型
EP3088018A1 (fr) 2015-04-30 2016-11-02 ECP Entwicklungsgesellschaft mbH Rotor pour une pompe à fluide et procédé et moule pour sa fabrication
EP3108909B1 (fr) * 2015-06-23 2018-09-26 Abiomed Europe GmbH Pompe sanguine
EP3808404A1 (fr) 2015-08-04 2021-04-21 Abiomed Europe GmbH Palier à auto-alignement
US9393384B1 (en) 2015-08-17 2016-07-19 Tufts Medical Center, Inc. Systems and methods for treating acute and chronic heart failure
US10279152B2 (en) 2015-08-17 2019-05-07 Tufts Medical Center, Inc. Systems and methods for treating acute and chronic heart failure
MA44837A (fr) 2015-08-25 2018-07-04 Innovein Inc Prothèse de valvule veineuse
US9821146B2 (en) 2015-09-22 2017-11-21 Abiomed, Inc. Guidewire for cannula placement
EP3153190A1 (fr) 2015-10-09 2017-04-12 ECP Entwicklungsgesellschaft mbH Pompe, notamment pompe a sang
EP3153191A1 (fr) 2015-10-09 2017-04-12 ECP Entwicklungsgesellschaft mbH Pompe a sang
EP3373828A1 (fr) 2015-11-09 2018-09-19 Revamp Medical Ltd. Réducteur de débit sanguin pour traitement cardiovasculaire
EP3928825A1 (fr) 2016-01-29 2021-12-29 Abiomed, Inc. Canule par thermoformage à rigidité variable du corps de canule
EP3205360B1 (fr) 2016-02-11 2018-08-29 Abiomed Europe GmbH Pompe sanguine
EP3222302B1 (fr) 2016-03-23 2018-05-16 Abiomed Europe GmbH Pompe sanguine avec filtre
ES2898827T3 (es) 2016-06-06 2022-03-09 Abiomed Inc Conjunto de bomba de sangre con sensor y protector de sensor
WO2018033920A1 (fr) 2016-08-18 2018-02-22 Angioslide Ltd. Cathéter d'administration de médicament et son procédé d'utilisation
EP3287154B1 (fr) 2016-08-23 2019-10-09 Abiomed Europe GmbH Dispositif d'assistance ventriculaire
IL248115A0 (en) 2016-09-28 2017-01-31 Yeda Res & Dev Thermoelectric device
EP3518825B1 (fr) 2016-09-29 2020-05-27 Magenta Medical Ltd. Tube pour vaisseau sanguin
EP3532120B1 (fr) 2016-10-25 2024-05-01 Magenta Medical Ltd. Dispositif d'assistance ventriculaire
WO2018083537A1 (fr) 2016-11-01 2018-05-11 White Swell Medical Ltd Systèmes et procédés de traitement de surcharge de liquides
US10179197B2 (en) 2016-11-21 2019-01-15 Cardiobridge Gmbh Catheter pump with a pump head for insertion into the aorta
EP3544649B1 (fr) 2016-11-23 2023-06-07 Magenta Medical Ltd. Pompes à sang
CA3054771A1 (fr) 2017-03-02 2018-09-07 White Swell Medical Ltd Systemes et methodes pour reduire la pression d'un debit sortant d'une conduite
WO2018172848A2 (fr) 2017-03-19 2018-09-27 White Swell Medical Ltd Procédés et dispositifs de réduction de pression
IL269815B2 (en) 2017-04-07 2024-05-01 Ecp Entw Mbh External drive unit for an implantable cardiac assist pump
US10926013B2 (en) 2017-04-07 2021-02-23 Ecp Entwicklungsgesellschaft Mbh Methods and systems for an external drive unit for an implantable heart assist pump
EP3398625A1 (fr) 2017-05-04 2018-11-07 Abiomed Europe GmbH Pompe à sang à cathéter renforcé
EP3398624A1 (fr) 2017-05-04 2018-11-07 Abiomed Europe GmbH Pompe à sang à cathéter renforcé
EP3630007A1 (fr) 2017-06-02 2020-04-08 Nephronyx Ltd. Modification d'écoulement dans des lumières corporelles
ES2870150T3 (es) 2017-08-22 2021-10-26 Ecp Entw Mbh Unidad de transmisión externa para una bomba de asistencia cardíaca implantable
ES2896901T3 (es) 2017-08-23 2022-02-28 Ecp Entw Mbh Cubierta del eje de accionamiento con una parte termoconductora
KR20200055753A (ko) 2017-09-14 2020-05-21 아비오메드, 인크. 의료 장치 유도자를 위한 통합된 확장 가능한 액세스
US20190183354A1 (en) 2017-12-18 2019-06-20 Edwards Lifesciences Corporation Monitoring blood pressure in the inferior vena cava
EP3508230A1 (fr) 2018-01-09 2019-07-10 Abiomed Europe GmbH Procédé et appareil d'étalonnage et utilisé lors de l'estimation du débit sanguin dans une pompe à sang intravasculaire
WO2019138350A2 (fr) 2018-01-10 2019-07-18 Magenta Medical Ltd Dispositif d'assistance ventriculaire
US10905808B2 (en) 2018-01-10 2021-02-02 Magenta Medical Ltd. Drive cable for use with a blood pump
US20200397963A1 (en) 2018-02-13 2020-12-24 White Swell Medical Ltd Intravascular catheters
WO2020018742A1 (fr) 2018-07-19 2020-01-23 Abiomed, Inc. Systèmes et procédés de réduction à partir d'un cathéter
US20200288988A1 (en) 2019-03-14 2020-09-17 Abiomed, Inc. Blood Flow Rate Measurement System
EP3858399A1 (fr) 2020-01-31 2021-08-04 ECP Entwicklungsgesellschaft mbH Pompe à sang intravasculaire
EP4100103A1 (fr) 2020-02-04 2022-12-14 Abiomed, Inc. Pompe d'assistance circulatoire intravasculaire avec filtre d'admission

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2013183060A2 (fr) 2012-06-06 2013-12-12 Magenta Medical Ltd. Valve rénale prothétique
US9597205B2 (en) 2012-06-06 2017-03-21 Magenta Medical Ltd. Prosthetic renal valve
WO2014141284A2 (fr) 2013-03-13 2014-09-18 Magenta Medical Ltd. Pompe rénale
US20160022890A1 (en) 2013-03-13 2016-01-28 Magenta Medical Ltd. Renal pump
US20170100527A1 (en) 2013-03-13 2017-04-13 Magenta Medical Ltd. Blood pump
US20150157777A1 (en) 2013-12-11 2015-06-11 Magenta Medical Ltd Curved catheter
US9764113B2 (en) 2013-12-11 2017-09-19 Magenta Medical Ltd Curved catheter
WO2015177793A2 (fr) 2014-05-19 2015-11-26 Magenta Medical Ltd. Pompe à sang
WO2016185473A1 (fr) 2015-05-18 2016-11-24 Magenta Medical Ltd. Pompe à sang

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US11648392B2 (en) 2023-05-16
AU2017364359A1 (en) 2019-05-02
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EP4233988A3 (fr) 2023-09-20
JP7094279B2 (ja) 2022-07-01
EP3544649B1 (fr) 2023-06-07
WO2018096531A1 (fr) 2018-05-31
US20210268261A1 (en) 2021-09-02
US20230233841A1 (en) 2023-07-27
CN110049792A (zh) 2019-07-23
US11033727B2 (en) 2021-06-15
CA3039302A1 (fr) 2018-05-31
EP3544649A1 (fr) 2019-10-02
CN110049792B (zh) 2022-01-18
US20190269840A1 (en) 2019-09-05

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